US20200221986A1 - Physiological monitoring devices, systems, and methods - Google Patents
Physiological monitoring devices, systems, and methods Download PDFInfo
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- US20200221986A1 US20200221986A1 US16/835,772 US202016835772A US2020221986A1 US 20200221986 A1 US20200221986 A1 US 20200221986A1 US 202016835772 A US202016835772 A US 202016835772A US 2020221986 A1 US2020221986 A1 US 2020221986A1
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Definitions
- the present disclosure relates to the field of non-invasive optical-based physiological monitoring sensors, and more particularly to systems, devices and methods for improving the non-invasive measurement accuracy of oxygen saturation, among other physiological parameters.
- Spectroscopy is a common technique for measuring the concentration of organic and some inorganic constituents of a solution.
- the theoretical basis of this technique is the Beer-Lambert law, which states that the concentration c i of an absorbent in solution can be determined by the intensity of light transmitted through the solution, knowing the pathlength d ⁇ , the intensity of the incident light I 0, ⁇ , and the extinction coefficient ⁇ i, ⁇ at a particular wavelength ⁇ .
- ⁇ ⁇ , ⁇ is the bulk absorption coefficient and represents the probability of absorption per unit length.
- the minimum number of discrete wavelengths that are required to solve equations 1 and 2 is the number of significant absorbers that are present in the solution.
- Pulse oximetry utilizes a noninvasive sensor to measure oxygen saturation and pulse rate, among other physiological parameters.
- Pulse oximetry relies on a sensor attached externally to the patient to output signals indicative of various physiological parameters, such as a patient's blood constituents and/or analytes, including for example a percent value for arterial oxygen saturation, among other physiological parameters.
- the sensor has an emitter that transmits optical radiation of one or more wavelengths into a tissue site and a detector that responds to the intensity of the optical radiation after absorption by pulsatile arterial blood flowing within the tissue site.
- a processor determines the relative concentrations of oxygenated hemoglobin (HbO 2 ) and deoxygenated hemoglobin (Hb) in the blood so as to derive oxygen saturation, which can provide early detection of potentially hazardous decreases in a patient's oxygen supply.
- HbO 2 oxygenated hemoglobin
- Hb deoxygenated hemoglobin
- a pulse oximetry system generally includes a patient monitor, a communications medium such as a cable, and/or a physiological sensor having one or more light emitters and a detector, such as one or more light-emitting diodes (LEDs) and a photodetector.
- the sensor is attached to a tissue site, such as a finger, toe, earlobe, nose, hand, foot, or other site having pulsatile blood flow which can be penetrated by light from the one or more emitters.
- the detector is responsive to the emitted light after attenuation or reflection by pulsatile blood flowing in the tissue site.
- the detector outputs a detector signal to the monitor over the communication medium.
- the monitor processes the signal to provide a numerical readout of physiological parameters such as oxygen saturation (SpO2) and/or pulse rate.
- a pulse oximetry sensor is described in U.S. Pat. No. 6,088,607 entitled Low Noise Optical Probe; pulse oximetry signal processing is described in U.S. Pat. Nos. 6,650,917 and 6,699,194 entitled Signal Processing Apparatus and Signal Processing Apparatus and Method, respectively; a pulse oximeter monitor is described in U.S. Pat. No. 6,584,336 entitled Universal/Upgrading Pulse Oximeter; all of which are assigned to Masimo Corporation, Irvine, Calif., and each is incorporated by reference herein in its entirety.
- pulse oximetry systems There are many sources of measurement error introduced to pulse oximetry systems. Some such sources of error include the pulse oximetry system's electronic components, including emitters and detectors, as well as chemical and structural physiological differences between patients. Another source of measurement error is the effect of multiple scattering of photons as the photons pass through the patient's tissue (arterial blood) and arrive at the sensor's light detector.
- This disclosure describes embodiments of non-invasive methods, devices, and systems for measuring blood constituents, analytes, and/or substances such as, by way of non-limiting example, oxygen, carboxyhemoglobin, methemoglobin, total hemoglobin, glucose, proteins, lipids, a percentage thereof (e.g., saturation), pulse rate, perfusion index, oxygen content, total hemoglobin, Oxygen Reserve IndexTM (ORITM) or for measuring many other physiologically relevant patient characteristics.
- oxygen carboxyhemoglobin
- methemoglobin total hemoglobin
- glucose proteins
- lipids a percentage thereof (e.g., saturation)
- pulse rate perfusion index
- oxygen content oxygen content
- total hemoglobin oxygen content
- Oxygen Reserve IndexTM ORITM
- an optical physiological measurement system includes an emitter configured to emit light of one or more wavelengths.
- the system also includes a diffuser configured to receive the emitted light, to spread the received light, and to emit the spread light over a larger tissue area than would otherwise be penetrated by the emitter directly emitting light at a tissue measurement site.
- the tissue measurement site can include, such as, for example, a finger, a wrist, or the like.
- the system further includes a concentrator configured to receive the spread light after it has been attenuated by or reflected from the tissue measurement site.
- the concentrator is also configured to collect and concentrate the received light and to emit the concentrated light to a detector.
- the detector is configured to detect the concentrated light and to transmit a signal indicative of the detected light.
- the system also includes a processor configured to receive the transmitted signal indicative of the detected light and to determine, based on an amount of absorption, an analyte of interest, such as, for example, arterial oxygen saturation or other parameter, in the tissue measurement site.
- the diffuser comprises glass, ground glass, glass beads, opal glass, or a microlens-based, band-limited, engineered diffuser that can deliver efficient and uniform illumination.
- the diffuser is further configured to define a surface area shape by which the emitted spread light is distributed onto a surface of the tissue measurement site.
- the defined surface area shape can include, by way of non-limiting example, a shape that is substantially rectangular, square, circular, oval, or annular, among others.
- the optical physiological measurement system includes an optical filter having a light-absorbing surface that faces the tissue measurement site.
- the optical filter also has an opening that is configured to allow the spread light, after being attenuated by the tissue measurement site, to be received by the concentrator.
- the opening has dimensions, wherein the dimensions of the opening are similar to the defined surface area shape by which the emitted spread light is distributed onto the surface of the tissue measurement site.
- the opening has dimensions that are larger than the defined surface area shape by which the emitted spread light is distributed onto the surface of the tissue measurement site.
- the dimensions of the opening in the optical filter are not the same as the diffuser opening, but the dimensions are larger than the detector package.
- the concentrator comprises glass, ground glass, glass beads, opal glass, or a compound parabolic concentrator.
- the concentrator comprises a cylindrical structure having a truncated circular conical structure on top. The truncated section is adjacent the detector.
- the light concentrator is structured to receive the emitted optical radiation, after reflection by the tissue measurement site, and to direct the reflected light to the detector.
- the processor is configured to determine an average level of the light detected by the detector.
- the average level of light is used to determine a physiological parameter in the tissue measurement site.
- a method to determine a constituent or analyte in a patient's blood includes emitting, from an emitter, light of at least one wavelength; spreading, with a diffuser, the emitted light and emitting the spread light from the diffuser to a tissue measurement site; receiving, by a concentrator, the spread light after the spread light has been attenuated by the tissue measurement site; concentrating, by the concentrator, the received light and emitting the concentrated light from the concentrator to a detector; detecting, with the detector, the emitted concentrated light; transmitting, from the detector, a signal responsive to the detected light; receiving, by a processor, the transmitted signal responsive to the detected light; and processing, by the processor, the received signal responsive to the detected light to determine a physiological parameter.
- the method to determine a constituent or analyte in a patient's blood includes filtering, with a light-absorbing detector filter, scattered portions of the emitted spread light.
- the light-absorbing detector filter is substantially rectangular in shape and has outer dimensions in the range of approximately 1-5 cm in width and approximately 2-8 cm in length, and has an opening through which emitted light may pass, the opening having dimensions in the range of approximately 0.25-3 cm in width and approximately 1-7 cm in length.
- the light-absorbing detector filter is substantially square in shape and has outer dimensions in the range of approximately 0.25-10 cm 2 , and has an opening through which emitted light may pass, the opening having dimensions in the range of approximately 0.1-8 cm 2 .
- the light-absorbing detector filter is substantially rectangular in shape and has outer dimensions of approximately 3 cm in width and approximately 6 cm in length, and has an opening through which emitted light may pass, the opening having dimensions of approximately 1.5 cm in width and approximately 4 cm in length.
- spreading, with a diffuser, the emitted light and emitting the spread light from the diffuser to a tissue measurement site is performed by at least one of a glass diffuser, a ground glass diffuser, a glass bead diffuser, an opal glass diffuser, and an engineered diffuser.
- the emitted spread light is emitted with a substantially uniform intensity profile.
- emitting the spread light from the diffuser to the tissue measurement site includes spreading the emitted light so as to define a surface area shape by which the emitted spread light is distributed onto a surface of the tissue measurement site.
- a pulse oximeter includes an emitter configured to emit light at one or more wavelengths.
- the pulse oximeter also includes a diffuser configured to receive the emitted light, to spread the received light, and to emit the spread light directed at a tissue measurement sight.
- the pulse oximeter also includes a detector configured to detect the emitted spread light after being attenuated by or reflected from the tissue measurement site and to transmit a signal indicative of the detected light.
- the pulse oximeter also includes a processor configured to receive the transmitted signal and to process the received signal to determine an average absorbance of a blood constituent or analyte in the tissue measurement site over a larger measurement site area than can be performed with a point light source or point detector.
- the diffuser is further configured to define a surface area shape by which the emitted spread light is distributed onto a surface of the tissue measurement site, and the detector is further configured to have a detection area corresponding to the defined surface area shape by which the emitted spread light is distributed onto the surface of the tissue measurement site.
- the detector comprises an array of detectors configured to cover the detection area.
- the processor is further configured to determine an average of the detected light.
- FIG. 1 illustrates a conventional approach to 2D pulse oximetry in which the emitter is configured to emit optical radiation as a point optical source.
- FIG. 2 illustrates the disclosed 3D approach to pulse oximetry in which the emitted light irradiates a substantially larger volume of tissue as compared to the point source approach described with respect to FIG. 2A .
- FIG. 3 illustrates schematically a side view of a 3D pulse oximetry sensor according to an embodiment of the present disclosure.
- FIG. 4A is a top view of a portion of a 3D pulse oximetry sensor according to an embodiment of the present disclosure.
- FIG. 4B illustrates the top view of a portion of the 3D pulse oximetry sensor shown in FIG. 4A , with the addition of a tissue measurement site in operational position.
- FIG. 5 illustrates a top view of a 3D pulse oximetry sensor according to an embodiment of the present disclosure.
- FIG. 6 illustrates a conventional 2D approach to reflective pulse oximetry in which the emitter is configured to emit optical radiation as a point optical source.
- FIG. 7A is a simplified schematic side view illustration of a reflective 3D pulse oximetry sensor according to an embodiment of the present disclosure.
- FIG. 7B is a simplified schematic top view illustration of the 3D reflective pulse oximetry sensor of FIG. 7A .
- FIG. 8 illustrates a block diagram of an example pulse oximetry system capable of noninvasively measuring one or more blood analytes in a monitored patient, according to an embodiment of the disclosure.
- FIG. 1 illustrates schematically a conventional pulse oximetry sensor having a two-dimensional (2D) approach to pulse oximetry.
- the emitter 104 is configured to emit optical radiation as a point optical source, i.e., an optical radiation source that has negligible dimensions such that it may be considered as a point.
- This approach is referred to herein as “two-dimensional” pulse oximetry because it applies a two-dimensional analytical model to the three-dimensional space of the tissue measurement site 102 of the patient.
- Point optical sources feature a defined, freely selectable, and homogeneous light beam area. Light beams emitted from LED point sources often exhibit a strong focus which can produce a usually sharply-defined and evenly-lit illuminated spot often with high intensity dynamics.
- tissue measurement site 102 when looking at the surface of the tissue measurement site 102 (or “sample tissue”), which in this example is a finger, a small point-like surface area of tissue 204 is irradiated by a point optical source.
- the irradiated circular area of the point optical source is in the range between 8 and 150 microns.
- the emitted point optical source of light enters the tissue measurement site 102 as a point of light. As the light penetrates the depth of the tissue 102 , it does so as a line or vector, representing a two-dimensional construct within a three-dimensional structure, namely the patient's tissue 102 .
- FIG. 2 illustrates schematically the disclosed systems, devices, and methods to implement three-dimensional (3D) pulse oximetry in which the emitted light irradiates a larger volume of tissue at the measurement site 102 as compared to the 2D point optical source approach described with respect to FIG. 1 .
- the irradiated surface area 206 of the measurement site 102 is substantially rectangular in shape with dimensions in the range of approximately 0.25-3 cm in width and approximately 1-6 cm in length.
- the irradiated surface area 206 of the measurement site 102 is substantially rectangular in shape and has dimensions of approximately 1.5 cm in width and approximately 2 cm in length.
- the irradiated surface area 206 of the measurement site 102 is substantially rectangular in shape and has dimensions of approximately 0.5 cm in width and approximately 1 cm in length. In another embodiment, the irradiated surface area 206 of the measurement site 102 is substantially rectangular in shape has dimensions of approximately 1 cm in width and approximately 1.5 cm in length. In yet another embodiment, the irradiated surface area 206 of the measurement site 102 is substantially square in shape and has dimensions in a range of approximately 0.25-9 cm 2 . In certain embodiments, the irradiated surface area 206 of the measurement site 102 is within a range of approximately 0.5-2 cm in width, and approximately 1-4 cm in length.
- irradiated surface area 206 can be used.
- the presently disclosed systems, devices, and methods apply a three-dimensional analytical model to the three-dimensional structure being measured, namely, the patient's sample tissue 102 .
- the amount of light absorbed by a substance is proportional to the concentration of the light-absorbing substance in the irradiated solution (i.e., arterial blood).
- a larger sample size of light attenuated (or reflected) by the tissue 102 is measured.
- the larger, 3D sample provides a data set that is more representative of the complete interaction of the emitted light as it passes through the patient's blood as compared to the 2D point source approach described above with respect to FIG. 1 .
- the disclosed pulse oximetry systems, devices, and methods will yield a more accurate measurement of the emitted light absorbed by the tissue, which will lead to a more accurate oxygen saturation measurement.
- FIG. 3 illustrates schematically a side view of a pulse oximetry 3D sensor 300 according to an embodiment of the present disclosure.
- the 3D sensor 300 irradiates the tissue measurement site 102 and detects the emitted light, after being attenuated by the tissue measurement site 102 .
- the 3D sensor 300 can be arranged to detect light that is reflected by the tissue measurement site 102 .
- the 3D sensor 300 includes an emitter 302 , a light diffuser 304 , a light-absorbing detector filter 306 , a light concentrator 308 , and a detector 310 .
- the 3D sensor 300 further includes a reflector 305 .
- the reflector 305 can be a metallic reflector or other type of reflector.
- Reflector 305 can be a coating, film, layer or other type of reflector.
- the reflector 305 can serve as a reflector to prevent emitted light from emitting out of a top portion of the light diffuser 304 such that light from the emitter 302 is directed in the tissue rather than escaping out of a side or top of the light diffuser 304 .
- the reflector 305 can prevent ambient light from entering the diffuser 304 which might ultimately cause errors within the detected light.
- the reflector 305 also prevent light piping that might occur if light from the detector 302 is able to escape from the light diffuser 304 and be pipped around a sensor securement mechanism to detector 310 without passing through the patient's tissue 102 .
- the emitter 302 can serve as the source of optical radiation transmitted towards the tissue measurement site 102 .
- the emitter 302 can include one or more sources of optical radiation, such as LEDs, laser diodes, incandescent bulbs with appropriate frequency-selective filters, combinations of the same, or the like.
- the emitter 302 includes sets of optical sources that are capable of emitting visible and near-infrared optical radiation.
- the emitter 302 transmits optical radiation of red and infrared wavelengths, at approximately 650 nm and approximately 940 nm, respectively.
- the emitter 302 includes a single source optical radiation.
- the light diffuser 304 receives the optical radiation emitted from the emitter 302 and spreads the optical radiation over an area, such as the area 206 depicted in FIG. 2 .
- the light diffuser 304 is a beam shaper that can homogenize the input light beam from the emitter 302 , shape the output intensity profile of the received light, and define the way (e.g., the shape or pattern) the emitted light is distributed to the tissue measurement site 102 .
- Examples of materials that can be used to realize the light diffuser 304 include, without limitation, a white surface, glass, ground glass, glass beads, polytetrafluoroethylene (also known as Teflon®, opal glass, and greyed glass, to name a few.
- engineered diffusers can be used to realize the diffuser 304 by providing customized light shaping with respect to intensity and distribution. Such diffusers can, for example, deliver substantially uniform illumination over a specified target area (such as, for example, irradiated surface area 206 ) in an energy-efficient manner. Examples of engineered diffusers can include molded plastics with specific shapes, patterns or textures designed to diffuse the emitter light across the entirety of the patient's tissue surface.
- the diffuser 304 can receive emitted light in the form of a point optical source and spread the light to fit a desired surface area on a plane defined by the surface of the tissue measurement site 102 .
- the diffuser 304 is made of ground glass which spreads the emitted light with a Gausian intensity profile.
- the diffuser 304 includes glass beads.
- the diffuser 304 is constructed so as to diffuse the emitted light in a Lambertian pattern.
- a Lambertian pattern is one in which the radiation intensity is substantially constant throughout the area of dispersion.
- One such diffuser 304 is made from opal glass.
- Opal glass is similar to ground glass, but has one surface coated with a milky white coating to diffuse light evenly.
- the diffuser 304 is capable of distributing the emitted light on the surface of a plane (e.g., the surface of the tissue measurement site 102 ) in a predefined geometry (e.g., a rectangle, square, or circle), and with a substantially uniform intensity profile and energy distribution.
- the efficiency, or the amount of light transmitted by the diffuser 304 is greater than 70% of the light emitted by the emitter 302 . In some embodiments, the efficiency is greater than 90% of the emitted light.
- Other optical elements known in the art may be used for the diffuser 304 .
- the diffuser 304 has a substantially rectangular shape having dimensions within a range of approximately 0.5-2 cm in width and approximately 1-4 centimeters in length. In another embodiment, the substantially rectangular shape of the diffuser 304 has dimensions of approximately 0.5 cm in width and approximately 1 cm in length. In another embodiment, the diffuser's 304 substantially rectangular shape has dimensions of approximately 1 cm in width and approximately 1.5 cm in length. In yet another embodiment, the diffuser 304 has a substantially square shape with dimensions in the range of approximately 0.25-10 cm 2 .
- the light-absorbing detector filter 306 which is also depicted in FIG. 4A in a top view, is a planar surface having an opening 402 through which the emitted light may pass after being attenuated by the tissue measurement site 102 .
- the opening 402 is rectangular-shaped, with dimensions substantially similar to the irradiated surface area 206 .
- the light-absorbing detector filter is substantially rectangular in shape and has outer dimensions of 4 cm in width and 8 cm in length, and has an opening through which emitted light may pass, the opening having dimensions of 2 cm in width and 5 cm in length.
- the light-absorbing detector filter is substantially rectangular in shape and has outer dimensions in the range of 1-3 cm in width and 2-8 cm in length, and has an opening through which emitted light may pass, the opening having dimensions in the range of 0.25-2 cm in width and 1-4 cm in length.
- the light-absorbing detector filter is substantially rectangular in shape and has outer dimensions of 3 cm in width and 6 cm in length, and has an opening through which emitted light may pass, the opening having dimensions of 1.5 cm in width and 4 cm in length.
- the top surface of the light-absorbing filter 306 (facing the tissue measurement site 102 and the emitter 302 ) is coated with a material that absorbs light, such as, for example, black pigment. Many other types of light-absorbing materials are well known in the art and can be used with the detector filter 306 .
- light emitted from the emitter 302 can reflect off of the tissue measurement site 102 (or other structures within the 3D sensor 300 ) to neighboring portions of the 3D sensor 300 . If those neighboring portions of the 3D sensor 300 possess reflective surfaces, then the light can reflect back to the tissue measurement site 102 , progress through the tissue and arrive at the detector 310 .
- the light-absorbing filter 306 reduces or eliminates the amount of emitted light that is reflected in this manner because it absorbs such reflected light, thereby stopping the chain of scattering events.
- the sensor-facing surfaces of other portions of the 3D sensor 300 are covered in light-absorbing material to further decrease the effect of reflective multiple scattering.
- the light concentrator 308 is a structure to receive the emitted optical radiation, after attenuation by the tissue measurement site 102 , to collect and concentrate the dispersed optical radiation, and to direct the collected and concentrated optical radiation to the detector 310 .
- the light concentrator 308 is made of ground glass or glass beads.
- the light concentrator 308 includes a compound parabolic concentrator.
- the detector 310 captures and measures light from the tissue measurement site 102 .
- the detector 310 can capture and measure light transmitted from the emitter 302 that has been attenuated by the tissue in the measurement site 102 .
- the detector 310 can output a detector signal responsive to the light captured or measured.
- the detector 310 can be implemented using one or more photodiodes, phototransistors, or the like.
- a plurality of detectors 310 can be arranged in an array with a spatial configuration corresponding to the irradiated surface area 206 to capture the attenuated or reflected light from the tissue measurement site.
- FIG. 4A a top view of a portion of the 3D sensor 300 is provided.
- the light-absorbing detector filter 306 is illustrated having a top surface coated with a light-absorbing material.
- the light-absorbing material can be a black opaque material or coating or any other dark color or coating configured to absorb light.
- a rectangular opening 402 is positioned relative to the light concentrator 308 (shown in phantom) and the detector 310 such that light may pass through the rectangular opening 402 , into the light concentrator 308 , and to the detector 310 .
- FIG. 4B illustrates the top view of a portion of the 3D sensor 300 as in FIG. 4A , with the addition of the tissue measurement site 102 in operational position.
- the rectangular opening 402 , the light concentrator 308 and the detector 310 are shown in phantom as being under the tissue measurement site 102 .
- the light concentrator 308 is shown to have dimensions significantly larger than the dimensions of the rectangular opening 402 .
- the dimensions of the light concentrator 308 , the rectangular opening 402 , and the irradiated surface area 206 are substantially similar.
- FIG. 5 illustrates a top view of a 3D pulse oximetry sensor 500 according to an embodiment of the present disclosure.
- the 3D sensor 500 is configured to be worn on a patient's finger 102 .
- the 3D sensor 500 includes an adhesive substrate 502 having front flaps 504 and rear flaps 506 extending outward from a center portion 508 of the 3D sensor 500 .
- the center portion 508 includes components of the 3D pulse oximetry sensor 300 described with respect to FIGS. 3, 4A and 4B .
- the emitter 302 and the light diffuser 304 are positioned on the front side of the adhesive substrate 502 .
- the light-absorbent detector filter 306 On the rear side of the adhesive substrate 502 the light-absorbent detector filter 306 , the light concentrator 308 and the detector 310 are positioned.
- the patient's finger serving as the tissue measurement site 102 is positioned over the rectangular opening 402 such that when the front portion of the adhesive substrate is folded over on top of the patient's finger 102 , the emitter 302 and the light diffuser 304 are aligned with the measurement site 102 , the filter 306 , the light concentrator 308 and the detector 310 .
- the front and rear flaps 504 , 506 can be wrapped around the finger measurement site 102 such that the adhesive substrate 502 provides a secure contact between the patient's skin and the 3D sensor 500 .
- FIG. 5 also illustrates an example of a sensor connector cable 510 which is used to connect the 3D sensor 500 to a monitor 809 , as described with respect to FIG. 8 .
- FIG. 6 is a simplified schematic illustration of a conventional, 2D approach to reflective pulse oximetry in which the emitter is configured to emit optical radiation as a point optical source.
- Reflective pulse oximetry is a method by which the emitter and detector are located on the same side of the tissue measurement site 102 . Light is emitted into a tissue measurement site 102 and attenuated. The emitted light passes into the tissue 102 and is then reflected back to the same side of the tissue measurement site 102 as the emitter.
- a depicted reflective 2D pulse oximetry sensor 600 includes an emitter 602 , a light block 606 , and a detector 610 .
- the light block 606 is necessary because the emitter 602 and the detector 610 are located on the same side of the tissue measurement site 102 . Accordingly, the light block 606 prevents incident emitter light, which did not enter the tissue measurement site 102 , from arriving at the detector 610 .
- the depicted 2D pulse oximetry sensor 600 is configured to emit light as a point source. As depicted in FIG. 6 , a simplified illustration of the light path 620 of the emitted light from the emitter 602 , through the tissue measurement site 102 , and to the detector 610 is provided. Notably, a point source of light is emitted, and a point source of light is detected. As discussed above with respect to FIG. 1 , use of a point optical source can result in substantial measurement error due to pathlength variability resulting from the multiple scatter phenomenon. The sample space provided by a 2D point optical emitter source is not large enough to account for pathlength variability, which will skew measurement results.
- FIGS. 7A and 7B are simplified schematic side and top views, respectively, of a 3D reflective pulse oximetry sensor 700 according to an embodiment of the present disclosure.
- the 3D sensor 700 irradiates the tissue measurement site 102 and detects the emitted light that is reflected by the tissue measurement site 102 .
- the 3D sensor 700 can be placed on a portion of the patient's body that has relatively flat surface, such as, for example a wrist, because the emitter 702 and detector 710 are on located the same side of the tissue measurement site 102 .
- the 3D sensor 700 includes an emitter 702 , a light diffuser 704 , a light block 706 , a light concentrator 708 , and a detector 710 .
- the emitter 702 can serve as the source of optical radiation transmitted towards the tissue measurement site 102 .
- the emitter 702 can include one or more sources of optical radiation.
- sources of optical radiation can include LEDs, laser diodes, incandescent bulbs with appropriate frequency-selective filters, combinations of the same, or the like.
- the emitter 702 includes sets of optical sources that are capable of emitting visible and near-infrared optical radiation.
- the emitter 702 transmits optical radiation of red and infrared wavelengths, at approximately 650 nm and approximately 940 nm, respectively.
- the emitter 702 includes a single source of optical radiation.
- the light diffuser 704 receives the optical radiation emitted from the emitter 302 and homogenously spreads the optical radiation over a wide, donut-shaped area, such as the area outlined by the light diffuser 704 as depicted in FIG. 7B .
- the diffuser 704 can receive emitted light in the form of a 2D point optical source (or any other form) and spread the light to fit the desired surface area on a plane defined by the surface of the tissue measurement site 102 .
- the diffuser 704 is made of ground glass or glass beads. A skilled artisan will understand that may other materials can be used to make the light diffuser 704 .
- the light blocker 706 includes an annular ring having a cover portion 707 sized and shaped to form a light isolation chamber for the light concentrator 708 and the detector 710 .
- the light block cover 707 is not illustrated in FIG. 7B .
- the light blocker 706 and the cover 707 can be made of any material that optically isolates the light concentrator 708 and the detector 710 .
- the light isolation chamber formed by the light blocker 706 and cover 708 ensures that the only light detected by the detector 710 is light that is reflected from the tissue measurement site.
- the light concentrator 708 is a cylindrical structure with a truncated circular conical structure on top, the truncated section of which of which is adjacent the detector 710 .
- the light concentrator 708 is structured to receive the emitted optical radiation, after reflection by the tissue measurement site 102 , and to direct the reflected light to the detector 710 .
- the light concentrator 708 is made of ground glass or glass beads.
- the light concentrator 708 includes a compound parabolic concentrator.
- the detector 710 captures and measures light from the tissue measurement site 102 .
- the detector 710 can capture and measure light transmitted from the emitter 702 that has been reflected from the tissue in the measurement site 102 .
- the detector 710 can output a detector signal responsive to the light captured or measured.
- the detector 710 can be implemented using one or more photodiodes, phototransistors, or the like.
- a plurality of detectors 710 can be arranged in an array with a spatial configuration corresponding to the irradiated surface area depicted in FIG. 7B by the light concentrator 708 to capture the reflected light from the tissue measurement site.
- the light path 720 illustrated in FIG. 7A depicts a substantial sample of reflected light that enter the light isolation chamber formed by the light blocker 706 and cover 707 .
- the large sample of reflected light (as compared to the reflected light collected using the 2D point optical source approach) provides the opportunity to take an average of the detected light, to derive a more accurate measurement of the emitted light absorbed by the tissue, which will lead to a more accurate oxygen saturation measurement.
- FIG. 7B a top view of the 3D sensor 700 is illustrated with both the emitter 702 and the light blocker cover 707 removed for ease of illustration.
- the outer ring illustrates the footprint of the light diffuser 704 .
- the light blocker 706 forms the circular wall of a light isolation chamber to keep incident light from being sensed by the detector 710 .
- the light blocker cover 707 blocks incidental light from entering the light isolation chamber from above.
- the light concentrator 710 collects the reflected light from the tissue measurement site 102 and funnels it upward toward the detector 710 at the center of the 3D sensor 700 .
- FIG. 8 illustrates an example of an optical physiological measurement system 800 , which may also be referred to herein as a pulse oximetry system 800 .
- the pulse oximetry system 800 noninvasively measures a blood analyte, such as oxygen, carboxyhemoglobin, methemoglobin, total hemoglobin, glucose, proteins, lipids, a percentage thereof (e.g., saturation), pulse rate, perfusion index, oxygen content, total hemoglobin, Oxygen Reserve IndexTM (ORITM) or many other physiologically relevant patient characteristics. These characteristics can relate to, for example, pulse rate, hydration, trending information and analysis, and the like.
- the system 800 can also measure additional blood analytes and/or other physiological parameters useful in determining a state or trend of wellness of a patient.
- the pulse oximetry system 800 can measure analyte concentrations at least in part by detecting optical radiation attenuated by tissue at a measurement site 102 .
- the measurement site 102 can be any location on a patient's body, such as a finger, foot, earlobe, wrist, forehead, or the like.
- the pulse oximetry system 800 can include a sensor 801 (or multiple sensors) that is coupled to a processing device or physiological monitor 809 .
- the sensor 801 and the monitor 809 are integrated together into a single unit.
- the sensor 801 and the monitor 809 are separate from each other and communicate with one another in any suitable manner, such as via a wired or wireless connection.
- the sensor 801 and monitor 809 can be attachable and detachable from each other for the convenience of the user or caregiver, for ease of storage, sterility issues, or the like.
- the senor 801 includes an emitter 804 , a detector 806 , and a front-end interface 808 .
- the emitter 804 can serve as the source of optical radiation transmitted towards measurement site 102 .
- the emitter 804 can include one or more sources of optical radiation, such as light emitting diodes (LEDs), laser diodes, incandescent bulbs with appropriate frequency-selective filters, combinations of the same, or the like.
- the emitter 804 includes sets of optical sources that are capable of emitting visible and near-infrared optical radiation.
- the pulse oximetry system 800 also includes a driver 811 that drives the emitter 804 .
- the driver 111 can be a circuit or the like that is controlled by the monitor 809 .
- the driver 811 can provide pulses of current to the emitter 804 .
- the driver 811 drives the emitter 804 in a progressive fashion, such as in an alternating manner.
- the driver 811 can drive the emitter 804 with a series of pulses for some wavelengths that can penetrate tissue relatively well and for other wavelengths that tend to be significantly absorbed in tissue.
- a wide variety of other driving powers and driving methodologies can be used in various embodiments.
- the driver 811 can be synchronized with other parts of the sensor 801 to minimize or reduce jitter in the timing of pulses of optical radiation emitted from the emitter 804 .
- the driver 811 is capable of driving the emitter 804 to emit optical radiation in a pattern that varies by less than about 10 parts-per-million.
- the detector 806 captures and measures light from the tissue measurement site 102 .
- the detector 806 can capture and measure light transmitted from the emitter 804 that has been attenuated or reflected from the tissue at the measurement site 102 .
- the detector 806 can output a detector signal 107 responsive to the light captured and measured.
- the detector 806 can be implemented using one or more photodiodes, phototransistors, or the like.
- a detector 806 is implemented in detector package to capture and measure light from the tissue measurement site 102 of the patient.
- the detector package can include a photodiode chip mounted to leads and enclosed in an encapsulant.
- the dimensions of the detector package are approximately 2 square centimeters. In other embodiments, the dimensions of the detector package are approximately 1.5 centimeters in width and approximately 2 centimeters in length.
- the front-end interface 808 provides an interface that adapts the output of the detectors 806 , which is responsive to desired physiological parameters.
- the front-end interface 808 can adapt the signal 807 received from the detector 806 into a form that can be processed by the monitor 809 , for example, by a signal processor 810 in the monitor 809 .
- the front-end interface 808 can have its components assembled in the sensor 801 , in the monitor 809 , in a connecting cabling (if used), in combinations of the same, or the like.
- the location of the front-end interface 808 can be chosen based on various factors including space desired for components, desired noise reductions or limits, desired heat reductions or limits, and the like.
- the front-end interface 808 can be coupled to the detector 806 and to the signal processor 810 using a bus, wire, electrical or optical cable, flex circuit, or some other form of signal connection.
- the front-end interface 808 can also be at least partially integrated with various components, such as the detectors 806 .
- the front-end interface 808 can include one or more integrated circuits that are on the same circuit board as the detector 806 . Other configurations can also be used.
- the monitor 909 can include the signal processor 810 and a user interface, such as a display 812 .
- the monitor 809 can also include optional outputs alone or in combination with the display 812 , such as a storage device 814 and a network interface 816 .
- the signal processor 810 includes processing logic that determines measurements for desired analytes based on the signals received from the detector 806 .
- the signal processor 810 can be implemented using one or more microprocessors or sub-processors (e.g., cores), digital signal processors, application specific integrated circuits (ASICs), field programmable gate arrays (FPGAs), combinations of the same, and the like.
- the signal processor 810 can provide various signals that control the operation of the sensor 801 .
- the signal processor 810 can provide an emitter control signal to the driver 811 .
- This control signal can be useful in order to synchronize, minimize, or reduce jitter in the timing of pulses emitted from the emitter 804 . Accordingly, this control signal can be useful in order to cause optical radiation pulses emitted from the emitter 804 to follow a precise timing and consistent pattern.
- the control signal from the signal processor 810 can provide synchronization with an analog-to-digital converter (ADC) in order to avoid aliasing, cross-talk, and the like.
- ADC analog-to-digital converter
- an optional memory 813 can be included in the front-end interface 808 and/or in the signal processor 810 .
- This memory 813 can serve as a buffer or storage location for the front-end interface 808 and/or the signal processor 810 , among other uses.
- the user interface 812 can provide an output, e.g., on a display, for presentation to a user of the pulse oximetry system 800 .
- the user interface 812 can be implemented as a touch-screen display, a liquid crystal display (LCD), an organic LED display, or the like.
- the pulse oximetry system 800 can be provided without a user interface 812 and can simply provide an output signal to a separate display or system.
- the storage device 814 and a network interface 816 represent other optional output connections that can be included in the monitor 809 .
- the storage device 814 can include any computer-readable medium, such as a memory device, hard disk storage, EEPROM, flash drive, or the like.
- the various software and/or firmware applications can be stored in the storage device 814 , which can be executed by the signal processor 810 or another processor of the monitor 809 .
- the network interface 816 can be a serial bus port (RS-232/RS-485), a Universal Serial Bus (USB) port, an Ethernet port, a wireless interface (e.g., WiFi such as any 802.1x interface, including an internal wireless card), or other suitable communication device(s) that allows the monitor 809 to communicate and share data with other devices.
- the monitor 809 can also include various other components not shown, such as a microprocessor, graphics processor, or controller to output the user interface 812 , to control data communications, to compute data trending, or to perform other operations.
- the pulse oximetry system 800 can include various other components or can be configured in different ways.
- the sensor 801 can have both the emitter 804 and detector 806 on the same side of the tissue measurement site 102 and use reflectance to measure analytes.
- the apparatuses and methods described herein may be implemented by one or more computer programs executed by one or more processors.
- the computer programs include processor-executable instructions that are stored on a non-transitory tangible computer readable medium.
- the computer programs may also include stored data.
- Non-limiting examples of the non-transitory tangible computer readable medium are nonvolatile memory, magnetic storage, and optical storage.
Abstract
Description
- The present application is a continuation of U.S. patent application Ser. No. 16/791,963, filed Feb. 14, 2020, which is a continuation of U.S. patent application Ser. No. 16/532,065 filed Aug. 5, 2019, which is a continuation of U.S. patent application Ser. No. 16/226,249 filed Dec. 19, 2018, which is a continuation of U.S. patent application Ser. No. 15/195,199 filed Jun. 28, 2016, which claims priority benefit under 35 U.S.C. § 119(e) from U.S. Provisional Application No. 62/188,430, filed Jul. 2, 2015, which is incorporated by reference herein. Any and all applications for which a foreign or domestic priority claim is identified in the Application Data Sheet as filed with the present application are hereby incorporated by reference under 37 CFR 1.57.
- The present disclosure relates to the field of non-invasive optical-based physiological monitoring sensors, and more particularly to systems, devices and methods for improving the non-invasive measurement accuracy of oxygen saturation, among other physiological parameters.
- Spectroscopy is a common technique for measuring the concentration of organic and some inorganic constituents of a solution. The theoretical basis of this technique is the Beer-Lambert law, which states that the concentration ci of an absorbent in solution can be determined by the intensity of light transmitted through the solution, knowing the pathlength dλ, the intensity of the incident light I0,λ, and the extinction coefficient εi,λ at a particular wavelength λ.
- In generalized form, the Beer-Lambert law is expressed as:
-
- where μα,λ is the bulk absorption coefficient and represents the probability of absorption per unit length. The minimum number of discrete wavelengths that are required to solve equations 1 and 2 is the number of significant absorbers that are present in the solution.
- A practical application of this technique is pulse oximetry, which utilizes a noninvasive sensor to measure oxygen saturation and pulse rate, among other physiological parameters. Pulse oximetry relies on a sensor attached externally to the patient to output signals indicative of various physiological parameters, such as a patient's blood constituents and/or analytes, including for example a percent value for arterial oxygen saturation, among other physiological parameters. The sensor has an emitter that transmits optical radiation of one or more wavelengths into a tissue site and a detector that responds to the intensity of the optical radiation after absorption by pulsatile arterial blood flowing within the tissue site. Based upon this response, a processor determines the relative concentrations of oxygenated hemoglobin (HbO2) and deoxygenated hemoglobin (Hb) in the blood so as to derive oxygen saturation, which can provide early detection of potentially hazardous decreases in a patient's oxygen supply.
- A pulse oximetry system generally includes a patient monitor, a communications medium such as a cable, and/or a physiological sensor having one or more light emitters and a detector, such as one or more light-emitting diodes (LEDs) and a photodetector. The sensor is attached to a tissue site, such as a finger, toe, earlobe, nose, hand, foot, or other site having pulsatile blood flow which can be penetrated by light from the one or more emitters. The detector is responsive to the emitted light after attenuation or reflection by pulsatile blood flowing in the tissue site. The detector outputs a detector signal to the monitor over the communication medium. The monitor processes the signal to provide a numerical readout of physiological parameters such as oxygen saturation (SpO2) and/or pulse rate. A pulse oximetry sensor is described in U.S. Pat. No. 6,088,607 entitled Low Noise Optical Probe; pulse oximetry signal processing is described in U.S. Pat. Nos. 6,650,917 and 6,699,194 entitled Signal Processing Apparatus and Signal Processing Apparatus and Method, respectively; a pulse oximeter monitor is described in U.S. Pat. No. 6,584,336 entitled Universal/Upgrading Pulse Oximeter; all of which are assigned to Masimo Corporation, Irvine, Calif., and each is incorporated by reference herein in its entirety.
- There are many sources of measurement error introduced to pulse oximetry systems. Some such sources of error include the pulse oximetry system's electronic components, including emitters and detectors, as well as chemical and structural physiological differences between patients. Another source of measurement error is the effect of multiple scattering of photons as the photons pass through the patient's tissue (arterial blood) and arrive at the sensor's light detector.
- This disclosure describes embodiments of non-invasive methods, devices, and systems for measuring blood constituents, analytes, and/or substances such as, by way of non-limiting example, oxygen, carboxyhemoglobin, methemoglobin, total hemoglobin, glucose, proteins, lipids, a percentage thereof (e.g., saturation), pulse rate, perfusion index, oxygen content, total hemoglobin, Oxygen Reserve Index™ (ORI™) or for measuring many other physiologically relevant patient characteristics. These characteristics can relate to, for example, pulse rate, hydration, trending information and analysis, and the like.
- In an embodiment, an optical physiological measurement system includes an emitter configured to emit light of one or more wavelengths. The system also includes a diffuser configured to receive the emitted light, to spread the received light, and to emit the spread light over a larger tissue area than would otherwise be penetrated by the emitter directly emitting light at a tissue measurement site. The tissue measurement site can include, such as, for example, a finger, a wrist, or the like. The system further includes a concentrator configured to receive the spread light after it has been attenuated by or reflected from the tissue measurement site. The concentrator is also configured to collect and concentrate the received light and to emit the concentrated light to a detector. The detector is configured to detect the concentrated light and to transmit a signal indicative of the detected light. The system also includes a processor configured to receive the transmitted signal indicative of the detected light and to determine, based on an amount of absorption, an analyte of interest, such as, for example, arterial oxygen saturation or other parameter, in the tissue measurement site.
- In certain embodiments of the present disclosure, the diffuser comprises glass, ground glass, glass beads, opal glass, or a microlens-based, band-limited, engineered diffuser that can deliver efficient and uniform illumination. In some embodiments the diffuser is further configured to define a surface area shape by which the emitted spread light is distributed onto a surface of the tissue measurement site. The defined surface area shape can include, by way of non-limiting example, a shape that is substantially rectangular, square, circular, oval, or annular, among others.
- According to some embodiments, the optical physiological measurement system includes an optical filter having a light-absorbing surface that faces the tissue measurement site. The optical filter also has an opening that is configured to allow the spread light, after being attenuated by the tissue measurement site, to be received by the concentrator. In an embodiment, the opening has dimensions, wherein the dimensions of the opening are similar to the defined surface area shape by which the emitted spread light is distributed onto the surface of the tissue measurement site. In an embodiment, the opening has dimensions that are larger than the defined surface area shape by which the emitted spread light is distributed onto the surface of the tissue measurement site. In other embodiments, the dimensions of the opening in the optical filter are not the same as the diffuser opening, but the dimensions are larger than the detector package.
- In other embodiments of the present disclosure, the concentrator comprises glass, ground glass, glass beads, opal glass, or a compound parabolic concentrator. In some embodiments the concentrator comprises a cylindrical structure having a truncated circular conical structure on top. The truncated section is adjacent the detector. The light concentrator is structured to receive the emitted optical radiation, after reflection by the tissue measurement site, and to direct the reflected light to the detector.
- In accordance with certain embodiments of the present disclosure, the processor is configured to determine an average level of the light detected by the detector. The average level of light is used to determine a physiological parameter in the tissue measurement site.
- According to another embodiment, a method to determine a constituent or analyte in a patient's blood is disclosed. The method includes emitting, from an emitter, light of at least one wavelength; spreading, with a diffuser, the emitted light and emitting the spread light from the diffuser to a tissue measurement site; receiving, by a concentrator, the spread light after the spread light has been attenuated by the tissue measurement site; concentrating, by the concentrator, the received light and emitting the concentrated light from the concentrator to a detector; detecting, with the detector, the emitted concentrated light; transmitting, from the detector, a signal responsive to the detected light; receiving, by a processor, the transmitted signal responsive to the detected light; and processing, by the processor, the received signal responsive to the detected light to determine a physiological parameter.
- In some embodiments, the method to determine a constituent or analyte in a patient's blood includes filtering, with a light-absorbing detector filter, scattered portions of the emitted spread light. According to an embodiment, the light-absorbing detector filter is substantially rectangular in shape and has outer dimensions in the range of approximately 1-5 cm in width and approximately 2-8 cm in length, and has an opening through which emitted light may pass, the opening having dimensions in the range of approximately 0.25-3 cm in width and approximately 1-7 cm in length. In another embodiment, the light-absorbing detector filter is substantially square in shape and has outer dimensions in the range of approximately 0.25-10 cm2, and has an opening through which emitted light may pass, the opening having dimensions in the range of approximately 0.1-8 cm2. In yet another embodiment, the light-absorbing detector filter is substantially rectangular in shape and has outer dimensions of approximately 3 cm in width and approximately 6 cm in length, and has an opening through which emitted light may pass, the opening having dimensions of approximately 1.5 cm in width and approximately 4 cm in length.
- In still other embodiments of the method to determine a constituent or analyte in a patient's blood, spreading, with a diffuser, the emitted light and emitting the spread light from the diffuser to a tissue measurement site is performed by at least one of a glass diffuser, a ground glass diffuser, a glass bead diffuser, an opal glass diffuser, and an engineered diffuser. In some embodiments the emitted spread light is emitted with a substantially uniform intensity profile. And in some embodiments, emitting the spread light from the diffuser to the tissue measurement site includes spreading the emitted light so as to define a surface area shape by which the emitted spread light is distributed onto a surface of the tissue measurement site.
- According to yet another embodiment, a pulse oximeter is disclosed. The pulse oximeter includes an emitter configured to emit light at one or more wavelengths. The pulse oximeter also includes a diffuser configured to receive the emitted light, to spread the received light, and to emit the spread light directed at a tissue measurement sight. The pulse oximeter also includes a detector configured to detect the emitted spread light after being attenuated by or reflected from the tissue measurement site and to transmit a signal indicative of the detected light. The pulse oximeter also includes a processor configured to receive the transmitted signal and to process the received signal to determine an average absorbance of a blood constituent or analyte in the tissue measurement site over a larger measurement site area than can be performed with a point light source or point detector. In some embodiments, the diffuser is further configured to define a surface area shape by which the emitted spread light is distributed onto a surface of the tissue measurement site, and the detector is further configured to have a detection area corresponding to the defined surface area shape by which the emitted spread light is distributed onto the surface of the tissue measurement site. According to some embodiments, the detector comprises an array of detectors configured to cover the detection area. In still other embodiments, the processor is further configured to determine an average of the detected light.
- For purposes of summarizing, certain aspects, advantages and novel features of the disclosure have been described herein. It is to be understood that not necessarily all such advantages can be achieved in accordance with any particular embodiment of the systems, devices and/or methods disclosed herein. Thus, the subject matter of the disclosure herein can be embodied or carried out in a manner that achieves or optimizes one advantage or group of advantages as taught herein without necessarily achieving other advantages as can be taught or suggested herein.
- Throughout the drawings, reference numbers can be re-used to indicate correspondence between referenced elements. The drawings are provided to illustrate embodiments of the disclosure described herein and not to limit the scope thereof.
-
FIG. 1 illustrates a conventional approach to 2D pulse oximetry in which the emitter is configured to emit optical radiation as a point optical source. -
FIG. 2 illustrates the disclosed 3D approach to pulse oximetry in which the emitted light irradiates a substantially larger volume of tissue as compared to the point source approach described with respect toFIG. 2A . -
FIG. 3 illustrates schematically a side view of a 3D pulse oximetry sensor according to an embodiment of the present disclosure. -
FIG. 4A is a top view of a portion of a 3D pulse oximetry sensor according to an embodiment of the present disclosure. -
FIG. 4B illustrates the top view of a portion of the 3D pulse oximetry sensor shown inFIG. 4A , with the addition of a tissue measurement site in operational position. -
FIG. 5 illustrates a top view of a 3D pulse oximetry sensor according to an embodiment of the present disclosure. -
FIG. 6 illustrates a conventional 2D approach to reflective pulse oximetry in which the emitter is configured to emit optical radiation as a point optical source. -
FIG. 7A is a simplified schematic side view illustration of a reflective 3D pulse oximetry sensor according to an embodiment of the present disclosure. -
FIG. 7B is a simplified schematic top view illustration of the 3D reflective pulse oximetry sensor ofFIG. 7A . -
FIG. 8 illustrates a block diagram of an example pulse oximetry system capable of noninvasively measuring one or more blood analytes in a monitored patient, according to an embodiment of the disclosure. -
FIG. 1 illustrates schematically a conventional pulse oximetry sensor having a two-dimensional (2D) approach to pulse oximetry. As illustrated, theemitter 104 is configured to emit optical radiation as a point optical source, i.e., an optical radiation source that has negligible dimensions such that it may be considered as a point. This approach is referred to herein as “two-dimensional” pulse oximetry because it applies a two-dimensional analytical model to the three-dimensional space of thetissue measurement site 102 of the patient. Point optical sources feature a defined, freely selectable, and homogeneous light beam area. Light beams emitted from LED point sources often exhibit a strong focus which can produce a usually sharply-defined and evenly-lit illuminated spot often with high intensity dynamics. Illustratively, when looking at the surface of the tissue measurement site 102 (or “sample tissue”), which in this example is a finger, a small point-like surface area of tissue 204 is irradiated by a point optical source. In some embodiments, the irradiated circular area of the point optical source is in the range between 8 and 150 microns. Illustratively, the emitted point optical source of light enters thetissue measurement site 102 as a point of light. As the light penetrates the depth of thetissue 102, it does so as a line or vector, representing a two-dimensional construct within a three-dimensional structure, namely the patient'stissue 102. - Use of a point optical source is believed to reduce variability in light pathlength which would lead to more accurate oximetry measurements. However, in practice, photons do not travel in straight paths. Instead, the light particles scatter, bouncing around between various irregular objects (such as, for example, red blood cells) in the patient's blood. Accordingly, photon pathlengths vary depending on, among other things, their particular journeys through and around the tissue at the
measurement site 102. This phenomenon is referred to as “multiple scattering.” In a study, the effects of multiple scattering were examined by comparing the results of photon diffusion analysis with those obtained using an analysis based on the Beer-Lambert law, which neglects multiple scattering in the determination of light pathlength. The study found that that the difference between the average lengths of the paths traveled by red and infrared photons makes the oximeter's calibration curve (based on measurements obtained from normal subjects) sensitive to the total attenuation coefficients of the tissue in the two wavelength bands used for pulse oximetry, as well as to absorption by the pulsating arterial blood. -
FIG. 2 illustrates schematically the disclosed systems, devices, and methods to implement three-dimensional (3D) pulse oximetry in which the emitted light irradiates a larger volume of tissue at themeasurement site 102 as compared to the 2D point optical source approach described with respect toFIG. 1 . In an embodiment, again looking at the surface of thetissue measurement site 102, theirradiated surface area 206 of themeasurement site 102 is substantially rectangular in shape with dimensions in the range of approximately 0.25-3 cm in width and approximately 1-6 cm in length. In another embodiment, theirradiated surface area 206 of themeasurement site 102 is substantially rectangular in shape and has dimensions of approximately 1.5 cm in width and approximately 2 cm in length. In another embodiment, theirradiated surface area 206 of themeasurement site 102 is substantially rectangular in shape and has dimensions of approximately 0.5 cm in width and approximately 1 cm in length. In another embodiment, theirradiated surface area 206 of themeasurement site 102 is substantially rectangular in shape has dimensions of approximately 1 cm in width and approximately 1.5 cm in length. In yet another embodiment, theirradiated surface area 206 of themeasurement site 102 is substantially square in shape and has dimensions in a range of approximately 0.25-9 cm2. In certain embodiments, theirradiated surface area 206 of themeasurement site 102 is within a range of approximately 0.5-2 cm in width, and approximately 1-4 cm in length. Of course a skilled artisan will appreciate that many other shapes and dimensions of irradiatedsurface area 206 can be used. Advantageously, by irradiating thetissue measurement site 102 with asurface area 206, the presently disclosed systems, devices, and methods apply a three-dimensional analytical model to the three-dimensional structure being measured, namely, the patient'ssample tissue 102. - According to the Beer-Lambert law, the amount of light absorbed by a substance is proportional to the concentration of the light-absorbing substance in the irradiated solution (i.e., arterial blood). Advantageously, by irradiating a larger volume of
tissue 102, a larger sample size of light attenuated (or reflected) by thetissue 102 is measured. The larger, 3D sample provides a data set that is more representative of the complete interaction of the emitted light as it passes through the patient's blood as compared to the 2D point source approach described above with respect toFIG. 1 . By taking an average of the detected light, as detected over a surface area substantially larger than a single point, the disclosed pulse oximetry systems, devices, and methods will yield a more accurate measurement of the emitted light absorbed by the tissue, which will lead to a more accurate oxygen saturation measurement. -
FIG. 3 illustrates schematically a side view of a pulseoximetry 3D sensor 300 according to an embodiment of the present disclosure. In the illustrated embodiment, the3D sensor 300 irradiates thetissue measurement site 102 and detects the emitted light, after being attenuated by thetissue measurement site 102. In other embodiments, for example, as describe below with respect toFIGS. 7A and 7B , the3D sensor 300 can be arranged to detect light that is reflected by thetissue measurement site 102. The3D sensor 300 includes anemitter 302, alight diffuser 304, a light-absorbingdetector filter 306, alight concentrator 308, and adetector 310. In some optional embodiments, the3D sensor 300 further includes areflector 305. Thereflector 305 can be a metallic reflector or other type of reflector.Reflector 305 can be a coating, film, layer or other type of reflector. Thereflector 305 can serve as a reflector to prevent emitted light from emitting out of a top portion of thelight diffuser 304 such that light from theemitter 302 is directed in the tissue rather than escaping out of a side or top of thelight diffuser 304. Additionally, thereflector 305 can prevent ambient light from entering thediffuser 304 which might ultimately cause errors within the detected light. Thereflector 305 also prevent light piping that might occur if light from thedetector 302 is able to escape from thelight diffuser 304 and be pipped around a sensor securement mechanism todetector 310 without passing through the patient'stissue 102. - The
emitter 302 can serve as the source of optical radiation transmitted towards thetissue measurement site 102. Theemitter 302 can include one or more sources of optical radiation, such as LEDs, laser diodes, incandescent bulbs with appropriate frequency-selective filters, combinations of the same, or the like. In an embodiment, theemitter 302 includes sets of optical sources that are capable of emitting visible and near-infrared optical radiation. In some embodiments, theemitter 302 transmits optical radiation of red and infrared wavelengths, at approximately 650 nm and approximately 940 nm, respectively. In some embodiments, theemitter 302 includes a single source optical radiation. - The
light diffuser 304 receives the optical radiation emitted from theemitter 302 and spreads the optical radiation over an area, such as thearea 206 depicted inFIG. 2 . In some embodiments, thelight diffuser 304 is a beam shaper that can homogenize the input light beam from theemitter 302, shape the output intensity profile of the received light, and define the way (e.g., the shape or pattern) the emitted light is distributed to thetissue measurement site 102. Examples of materials that can be used to realize thelight diffuser 304 include, without limitation, a white surface, glass, ground glass, glass beads, polytetrafluoroethylene (also known as Teflon®, opal glass, and greyed glass, to name a few. Additionally, engineered diffusers can be used to realize thediffuser 304 by providing customized light shaping with respect to intensity and distribution. Such diffusers can, for example, deliver substantially uniform illumination over a specified target area (such as, for example, irradiated surface area 206) in an energy-efficient manner. Examples of engineered diffusers can include molded plastics with specific shapes, patterns or textures designed to diffuse the emitter light across the entirety of the patient's tissue surface. - Advantageously, the
diffuser 304 can receive emitted light in the form of a point optical source and spread the light to fit a desired surface area on a plane defined by the surface of thetissue measurement site 102. In an embodiment, thediffuser 304 is made of ground glass which spreads the emitted light with a Gausian intensity profile. In another embodiment thediffuser 304 includes glass beads. In some embodiments, thediffuser 304 is constructed so as to diffuse the emitted light in a Lambertian pattern. A Lambertian pattern is one in which the radiation intensity is substantially constant throughout the area of dispersion. Onesuch diffuser 304 is made from opal glass. Opal glass is similar to ground glass, but has one surface coated with a milky white coating to diffuse light evenly. In an embodiment, thediffuser 304 is capable of distributing the emitted light on the surface of a plane (e.g., the surface of the tissue measurement site 102) in a predefined geometry (e.g., a rectangle, square, or circle), and with a substantially uniform intensity profile and energy distribution. In some embodiments, the efficiency, or the amount of light transmitted by thediffuser 304, is greater than 70% of the light emitted by theemitter 302. In some embodiments, the efficiency is greater than 90% of the emitted light. Other optical elements known in the art may be used for thediffuser 304. - In an embodiment, the
diffuser 304 has a substantially rectangular shape having dimensions within a range of approximately 0.5-2 cm in width and approximately 1-4 centimeters in length. In another embodiment, the substantially rectangular shape of thediffuser 304 has dimensions of approximately 0.5 cm in width and approximately 1 cm in length. In another embodiment, the diffuser's 304 substantially rectangular shape has dimensions of approximately 1 cm in width and approximately 1.5 cm in length. In yet another embodiment, thediffuser 304 has a substantially square shape with dimensions in the range of approximately 0.25-10 cm2. - The light-absorbing
detector filter 306, which is also depicted inFIG. 4A in a top view, is a planar surface having anopening 402 through which the emitted light may pass after being attenuated by thetissue measurement site 102. In the depicted embodiment, theopening 402 is rectangular-shaped, with dimensions substantially similar to theirradiated surface area 206. According to an embodiment, the light-absorbing detector filter is substantially rectangular in shape and has outer dimensions of 4 cm in width and 8 cm in length, and has an opening through which emitted light may pass, the opening having dimensions of 2 cm in width and 5 cm in length. In another embodiment, the light-absorbing detector filter is substantially rectangular in shape and has outer dimensions in the range of 1-3 cm in width and 2-8 cm in length, and has an opening through which emitted light may pass, the opening having dimensions in the range of 0.25-2 cm in width and 1-4 cm in length. In yet another embodiment, the light-absorbing detector filter is substantially rectangular in shape and has outer dimensions of 3 cm in width and 6 cm in length, and has an opening through which emitted light may pass, the opening having dimensions of 1.5 cm in width and 4 cm in length. - The top surface of the light-absorbing filter 306 (facing the
tissue measurement site 102 and the emitter 302) is coated with a material that absorbs light, such as, for example, black pigment. Many other types of light-absorbing materials are well known in the art and can be used with thedetector filter 306. During operation, light emitted from theemitter 302 can reflect off of the tissue measurement site 102 (or other structures within the 3D sensor 300) to neighboring portions of the3D sensor 300. If those neighboring portions of the3D sensor 300 possess reflective surfaces, then the light can reflect back to thetissue measurement site 102, progress through the tissue and arrive at thedetector 310. Such multiple scattering can result in detecting photons whose pathlengths are considerably longer than most of the light that is detected, thereby introducing variations in pathlength which will affect the accuracy of the measurements of the pulseoximetry 3D sensor 300. Advantageously, the light-absorbingfilter 306 reduces or eliminates the amount of emitted light that is reflected in this manner because it absorbs such reflected light, thereby stopping the chain of scattering events. In certain embodiments, the sensor-facing surfaces of other portions of the3D sensor 300 are covered in light-absorbing material to further decrease the effect of reflective multiple scattering. - The
light concentrator 308 is a structure to receive the emitted optical radiation, after attenuation by thetissue measurement site 102, to collect and concentrate the dispersed optical radiation, and to direct the collected and concentrated optical radiation to thedetector 310. In an embodiment, thelight concentrator 308 is made of ground glass or glass beads. In some embodiments, thelight concentrator 308 includes a compound parabolic concentrator. - As described above with respect to
FIG. 1 , thedetector 310 captures and measures light from thetissue measurement site 102. For example, thedetector 310 can capture and measure light transmitted from theemitter 302 that has been attenuated by the tissue in themeasurement site 102. Thedetector 310 can output a detector signal responsive to the light captured or measured. Thedetector 310 can be implemented using one or more photodiodes, phototransistors, or the like. In addition, a plurality ofdetectors 310 can be arranged in an array with a spatial configuration corresponding to theirradiated surface area 206 to capture the attenuated or reflected light from the tissue measurement site. - Referring to
FIG. 4A , a top view of a portion of the3D sensor 300 is provided. The light-absorbingdetector filter 306 is illustrated having a top surface coated with a light-absorbing material. The light-absorbing material can be a black opaque material or coating or any other dark color or coating configured to absorb light. Additionally, arectangular opening 402 is positioned relative to the light concentrator 308 (shown in phantom) and thedetector 310 such that light may pass through therectangular opening 402, into thelight concentrator 308, and to thedetector 310.FIG. 4B illustrates the top view of a portion of the3D sensor 300 as inFIG. 4A , with the addition of thetissue measurement site 102 in operational position. Accordingly, therectangular opening 402, thelight concentrator 308 and thedetector 310 are shown in phantom as being under thetissue measurement site 102. InFIGS. 4A and 4B , thelight concentrator 308 is shown to have dimensions significantly larger than the dimensions of therectangular opening 402. In other embodiments, the dimensions of thelight concentrator 308, therectangular opening 402, and theirradiated surface area 206 are substantially similar. -
FIG. 5 illustrates a top view of a 3D pulse oximetry sensor 500 according to an embodiment of the present disclosure. The 3D sensor 500 is configured to be worn on a patient'sfinger 102. The 3D sensor 500 includes anadhesive substrate 502 havingfront flaps 504 andrear flaps 506 extending outward from acenter portion 508 of the 3D sensor 500. Thecenter portion 508 includes components of the 3Dpulse oximetry sensor 300 described with respect toFIGS. 3, 4A and 4B . On the front side of theadhesive substrate 502 theemitter 302 and thelight diffuser 304 are positioned. On the rear side of theadhesive substrate 502 the light-absorbent detector filter 306, thelight concentrator 308 and thedetector 310 are positioned. In use, the patient's finger serving as thetissue measurement site 102 is positioned over therectangular opening 402 such that when the front portion of the adhesive substrate is folded over on top of the patient'sfinger 102, theemitter 302 and thelight diffuser 304 are aligned with themeasurement site 102, thefilter 306, thelight concentrator 308 and thedetector 310. Once alignment is established, the front andrear flaps finger measurement site 102 such that theadhesive substrate 502 provides a secure contact between the patient's skin and the 3D sensor 500.FIG. 5 also illustrates an example of asensor connector cable 510 which is used to connect the 3D sensor 500 to amonitor 809, as described with respect toFIG. 8 . -
FIG. 6 is a simplified schematic illustration of a conventional, 2D approach to reflective pulse oximetry in which the emitter is configured to emit optical radiation as a point optical source. Reflective pulse oximetry is a method by which the emitter and detector are located on the same side of thetissue measurement site 102. Light is emitted into atissue measurement site 102 and attenuated. The emitted light passes into thetissue 102 and is then reflected back to the same side of thetissue measurement site 102 as the emitter. As illustrated inFIG. 6 , a depicted reflective 2Dpulse oximetry sensor 600 includes anemitter 602, alight block 606, and adetector 610. Thelight block 606 is necessary because theemitter 602 and thedetector 610 are located on the same side of thetissue measurement site 102. Accordingly, thelight block 606 prevents incident emitter light, which did not enter thetissue measurement site 102, from arriving at thedetector 610. The depicted 2Dpulse oximetry sensor 600 is configured to emit light as a point source. As depicted inFIG. 6 , a simplified illustration of thelight path 620 of the emitted light from theemitter 602, through thetissue measurement site 102, and to thedetector 610 is provided. Notably, a point source of light is emitted, and a point source of light is detected. As discussed above with respect toFIG. 1 , use of a point optical source can result in substantial measurement error due to pathlength variability resulting from the multiple scatter phenomenon. The sample space provided by a 2D point optical emitter source is not large enough to account for pathlength variability, which will skew measurement results. -
FIGS. 7A and 7B are simplified schematic side and top views, respectively, of a 3D reflectivepulse oximetry sensor 700 according to an embodiment of the present disclosure. In the illustrated embodiment, the3D sensor 700 irradiates thetissue measurement site 102 and detects the emitted light that is reflected by thetissue measurement site 102. The3D sensor 700 can be placed on a portion of the patient's body that has relatively flat surface, such as, for example a wrist, because theemitter 702 anddetector 710 are on located the same side of thetissue measurement site 102. The3D sensor 700 includes anemitter 702, alight diffuser 704, alight block 706, alight concentrator 708, and adetector 710. - As previously described, the
emitter 702 can serve as the source of optical radiation transmitted towards thetissue measurement site 102. Theemitter 702 can include one or more sources of optical radiation. Such sources of optical radiation can include LEDs, laser diodes, incandescent bulbs with appropriate frequency-selective filters, combinations of the same, or the like. In an embodiment, theemitter 702 includes sets of optical sources that are capable of emitting visible and near-infrared optical radiation. In some embodiments, theemitter 702 transmits optical radiation of red and infrared wavelengths, at approximately 650 nm and approximately 940 nm, respectively. In some embodiments, theemitter 702 includes a single source of optical radiation. - The
light diffuser 704 receives the optical radiation emitted from theemitter 302 and homogenously spreads the optical radiation over a wide, donut-shaped area, such as the area outlined by thelight diffuser 704 as depicted inFIG. 7B . Advantageously, thediffuser 704 can receive emitted light in the form of a 2D point optical source (or any other form) and spread the light to fit the desired surface area on a plane defined by the surface of thetissue measurement site 102. In an embodiment, thediffuser 704 is made of ground glass or glass beads. A skilled artisan will understand that may other materials can be used to make thelight diffuser 704. - The
light blocker 706 includes an annular ring having acover portion 707 sized and shaped to form a light isolation chamber for thelight concentrator 708 and thedetector 710. (For purposes of illustration, thelight block cover 707 is not illustrated inFIG. 7B .) Thelight blocker 706 and thecover 707 can be made of any material that optically isolates thelight concentrator 708 and thedetector 710. The light isolation chamber formed by thelight blocker 706 and cover 708 ensures that the only light detected by thedetector 710 is light that is reflected from the tissue measurement site. - The
light concentrator 708 is a cylindrical structure with a truncated circular conical structure on top, the truncated section of which of which is adjacent thedetector 710. Thelight concentrator 708 is structured to receive the emitted optical radiation, after reflection by thetissue measurement site 102, and to direct the reflected light to thedetector 710. In an embodiment, thelight concentrator 708 is made of ground glass or glass beads. In some embodiments, thelight concentrator 708 includes a compound parabolic concentrator. - As previously described, the
detector 710 captures and measures light from thetissue measurement site 102. For example, thedetector 710 can capture and measure light transmitted from theemitter 702 that has been reflected from the tissue in themeasurement site 102. Thedetector 710 can output a detector signal responsive to the light captured or measured. Thedetector 710 can be implemented using one or more photodiodes, phototransistors, or the like. In addition, a plurality ofdetectors 710 can be arranged in an array with a spatial configuration corresponding to the irradiated surface area depicted inFIG. 7B by thelight concentrator 708 to capture the reflected light from the tissue measurement site. - Advantageously, the
light path 720 illustrated inFIG. 7A depicts a substantial sample of reflected light that enter the light isolation chamber formed by thelight blocker 706 andcover 707. As previously discussed, the large sample of reflected light (as compared to the reflected light collected using the 2D point optical source approach) provides the opportunity to take an average of the detected light, to derive a more accurate measurement of the emitted light absorbed by the tissue, which will lead to a more accurate oxygen saturation measurement. - Referring now to
FIG. 7B , a top view of the3D sensor 700 is illustrated with both theemitter 702 and thelight blocker cover 707 removed for ease of illustration. The outer ring illustrates the footprint of thelight diffuser 704. As light is emitted from the emitter 702 (not shown inFIG. 7B ), it is diffused homogenously and directed to thetissue measurement site 102. Thelight blocker 706 forms the circular wall of a light isolation chamber to keep incident light from being sensed by thedetector 710. Thelight blocker cover 707 blocks incidental light from entering the light isolation chamber from above. Thelight concentrator 710 collects the reflected light from thetissue measurement site 102 and funnels it upward toward thedetector 710 at the center of the3D sensor 700. -
FIG. 8 illustrates an example of an opticalphysiological measurement system 800, which may also be referred to herein as apulse oximetry system 800. In certain embodiments, thepulse oximetry system 800 noninvasively measures a blood analyte, such as oxygen, carboxyhemoglobin, methemoglobin, total hemoglobin, glucose, proteins, lipids, a percentage thereof (e.g., saturation), pulse rate, perfusion index, oxygen content, total hemoglobin, Oxygen Reserve Index™ (ORI™) or many other physiologically relevant patient characteristics. These characteristics can relate to, for example, pulse rate, hydration, trending information and analysis, and the like. Thesystem 800 can also measure additional blood analytes and/or other physiological parameters useful in determining a state or trend of wellness of a patient. - The
pulse oximetry system 800 can measure analyte concentrations at least in part by detecting optical radiation attenuated by tissue at ameasurement site 102. Themeasurement site 102 can be any location on a patient's body, such as a finger, foot, earlobe, wrist, forehead, or the like. - The
pulse oximetry system 800 can include a sensor 801 (or multiple sensors) that is coupled to a processing device orphysiological monitor 809. In an embodiment, thesensor 801 and themonitor 809 are integrated together into a single unit. In another embodiment, thesensor 801 and themonitor 809 are separate from each other and communicate with one another in any suitable manner, such as via a wired or wireless connection. Thesensor 801 and monitor 809 can be attachable and detachable from each other for the convenience of the user or caregiver, for ease of storage, sterility issues, or the like. - In the depicted embodiment shown in
FIG. 8 , thesensor 801 includes anemitter 804, adetector 806, and a front-end interface 808. Theemitter 804 can serve as the source of optical radiation transmitted towardsmeasurement site 102. Theemitter 804 can include one or more sources of optical radiation, such as light emitting diodes (LEDs), laser diodes, incandescent bulbs with appropriate frequency-selective filters, combinations of the same, or the like. In an embodiment, theemitter 804 includes sets of optical sources that are capable of emitting visible and near-infrared optical radiation. - The
pulse oximetry system 800 also includes adriver 811 that drives theemitter 804. Thedriver 111 can be a circuit or the like that is controlled by themonitor 809. For example, thedriver 811 can provide pulses of current to theemitter 804. In an embodiment, thedriver 811 drives theemitter 804 in a progressive fashion, such as in an alternating manner. Thedriver 811 can drive theemitter 804 with a series of pulses for some wavelengths that can penetrate tissue relatively well and for other wavelengths that tend to be significantly absorbed in tissue. A wide variety of other driving powers and driving methodologies can be used in various embodiments. Thedriver 811 can be synchronized with other parts of thesensor 801 to minimize or reduce jitter in the timing of pulses of optical radiation emitted from theemitter 804. In some embodiments, thedriver 811 is capable of driving theemitter 804 to emit optical radiation in a pattern that varies by less than about 10 parts-per-million. - The
detector 806 captures and measures light from thetissue measurement site 102. For example, thedetector 806 can capture and measure light transmitted from theemitter 804 that has been attenuated or reflected from the tissue at themeasurement site 102. Thedetector 806 can output a detector signal 107 responsive to the light captured and measured. Thedetector 806 can be implemented using one or more photodiodes, phototransistors, or the like. In some embodiments, adetector 806 is implemented in detector package to capture and measure light from thetissue measurement site 102 of the patient. The detector package can include a photodiode chip mounted to leads and enclosed in an encapsulant. In some embodiments, the dimensions of the detector package are approximately 2 square centimeters. In other embodiments, the dimensions of the detector package are approximately 1.5 centimeters in width and approximately 2 centimeters in length. - The front-
end interface 808 provides an interface that adapts the output of thedetectors 806, which is responsive to desired physiological parameters. For example, the front-end interface 808 can adapt thesignal 807 received from thedetector 806 into a form that can be processed by themonitor 809, for example, by asignal processor 810 in themonitor 809. The front-end interface 808 can have its components assembled in thesensor 801, in themonitor 809, in a connecting cabling (if used), in combinations of the same, or the like. The location of the front-end interface 808 can be chosen based on various factors including space desired for components, desired noise reductions or limits, desired heat reductions or limits, and the like. - The front-
end interface 808 can be coupled to thedetector 806 and to thesignal processor 810 using a bus, wire, electrical or optical cable, flex circuit, or some other form of signal connection. The front-end interface 808 can also be at least partially integrated with various components, such as thedetectors 806. For example, the front-end interface 808 can include one or more integrated circuits that are on the same circuit board as thedetector 806. Other configurations can also be used. - As shown in
FIG. 8 , the monitor 909 can include thesignal processor 810 and a user interface, such as adisplay 812. Themonitor 809 can also include optional outputs alone or in combination with thedisplay 812, such as astorage device 814 and anetwork interface 816. In an embodiment, thesignal processor 810 includes processing logic that determines measurements for desired analytes based on the signals received from thedetector 806. Thesignal processor 810 can be implemented using one or more microprocessors or sub-processors (e.g., cores), digital signal processors, application specific integrated circuits (ASICs), field programmable gate arrays (FPGAs), combinations of the same, and the like. - The
signal processor 810 can provide various signals that control the operation of thesensor 801. For example, thesignal processor 810 can provide an emitter control signal to thedriver 811. This control signal can be useful in order to synchronize, minimize, or reduce jitter in the timing of pulses emitted from theemitter 804. Accordingly, this control signal can be useful in order to cause optical radiation pulses emitted from theemitter 804 to follow a precise timing and consistent pattern. For example, when a transimpedance-based front-end interface 808 is used, the control signal from thesignal processor 810 can provide synchronization with an analog-to-digital converter (ADC) in order to avoid aliasing, cross-talk, and the like. As also shown, anoptional memory 813 can be included in the front-end interface 808 and/or in thesignal processor 810. Thismemory 813 can serve as a buffer or storage location for the front-end interface 808 and/or thesignal processor 810, among other uses. - The
user interface 812 can provide an output, e.g., on a display, for presentation to a user of thepulse oximetry system 800. Theuser interface 812 can be implemented as a touch-screen display, a liquid crystal display (LCD), an organic LED display, or the like. In alternative embodiments, thepulse oximetry system 800 can be provided without auser interface 812 and can simply provide an output signal to a separate display or system. - The
storage device 814 and anetwork interface 816 represent other optional output connections that can be included in themonitor 809. Thestorage device 814 can include any computer-readable medium, such as a memory device, hard disk storage, EEPROM, flash drive, or the like. The various software and/or firmware applications can be stored in thestorage device 814, which can be executed by thesignal processor 810 or another processor of themonitor 809. Thenetwork interface 816 can be a serial bus port (RS-232/RS-485), a Universal Serial Bus (USB) port, an Ethernet port, a wireless interface (e.g., WiFi such as any 802.1x interface, including an internal wireless card), or other suitable communication device(s) that allows themonitor 809 to communicate and share data with other devices. Themonitor 809 can also include various other components not shown, such as a microprocessor, graphics processor, or controller to output theuser interface 812, to control data communications, to compute data trending, or to perform other operations. - Although not shown in the depicted embodiment, the
pulse oximetry system 800 can include various other components or can be configured in different ways. For example, thesensor 801 can have both theemitter 804 anddetector 806 on the same side of thetissue measurement site 102 and use reflectance to measure analytes. - Although the foregoing disclosure has been described in terms of certain preferred embodiments, many other variations than those described herein will be apparent to those of ordinary skill in the art.
- Conditional language used herein, such as, among others, “can,” “might,” “may,” “e.g.,” and the like, unless specifically stated otherwise, or otherwise understood within the context as used, is generally intended to convey that certain embodiments include, while other embodiments do not include, certain features, elements and/or states. Thus, such conditional language is not generally intended to imply that features, elements and/or states are in any way required for one or more embodiments or that one or more embodiments necessarily include logic for deciding, with or without author input or prompting, whether these features, elements and/or states are included or are to be performed in any particular embodiment. The terms “comprising,” “including,” “having,” and the like are synonymous and are used inclusively, in an open-ended fashion, and do not exclude additional elements, features, acts, operations, and so forth. Also, the term “or” is used in its inclusive sense (and not in its exclusive sense) so that when used, for example, to connect a list of elements, the term “or” means one, some, or all of the elements in the list. Further, the term “each,” as used herein, in addition to having its ordinary meaning, can mean any subset of a set of elements to which the term “each” is applied.
- While the above detailed description has shown, described, and pointed out novel features as applied to various embodiments, it will be understood that various omissions, substitutions, and changes in the form and details of the systems, devices or algorithms illustrated can be made without departing from the spirit of the disclosure. As will be recognized, certain embodiments of the disclosure described herein can be embodied within a form that does not provide all of the features and benefits set forth herein, as some features can be used or practiced separately from others.
- The term “and/or” herein has its broadest, least limiting meaning which is the disclosure includes A alone, B alone, both A and B together, or A or B alternatively, but does not require both A and B or require one of A or one of B. As used herein, the phrase “at least one of” A, B, “and” C should be construed to mean a logical A or B or C, using a non-exclusive logical or.
- The apparatuses and methods described herein may be implemented by one or more computer programs executed by one or more processors. The computer programs include processor-executable instructions that are stored on a non-transitory tangible computer readable medium. The computer programs may also include stored data. Non-limiting examples of the non-transitory tangible computer readable medium are nonvolatile memory, magnetic storage, and optical storage. Although the foregoing disclosure has been described in terms of certain preferred embodiments, other embodiments will be apparent to those of ordinary skill in the art from the disclosure herein. Additionally, other combinations, omissions, substitutions and modifications will be apparent to the skilled artisan in view of the disclosure herein. Accordingly, the present invention is not intended to be limited by the description of the preferred embodiments, but is to be defined by reference to claims.
- Additionally, all publications, patents, and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication, patent, or patent application were specifically and individually indicated to be incorporated by reference.
Claims (29)
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US15/195,199 US10448871B2 (en) | 2015-07-02 | 2016-06-28 | Advanced pulse oximetry sensor |
US16/226,249 US10470695B2 (en) | 2015-07-02 | 2018-12-19 | Advanced pulse oximetry sensor |
US16/532,065 US10646146B2 (en) | 2015-07-02 | 2019-08-05 | Physiological monitoring devices, systems, and methods |
US16/791,963 US10722159B2 (en) | 2015-07-02 | 2020-02-14 | Physiological monitoring devices, systems, and methods |
US16/835,772 US10687745B1 (en) | 2015-07-02 | 2020-03-31 | Physiological monitoring devices, systems, and methods |
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Families Citing this family (198)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE60139128D1 (en) | 2000-08-18 | 2009-08-13 | Masimo Corp | PULSE OXIMETER WITH TWO OPERATING MODES |
US6697658B2 (en) | 2001-07-02 | 2004-02-24 | Masimo Corporation | Low power pulse oximeter |
US7355512B1 (en) | 2002-01-24 | 2008-04-08 | Masimo Corporation | Parallel alarm processor |
US6850788B2 (en) | 2002-03-25 | 2005-02-01 | Masimo Corporation | Physiological measurement communications adapter |
US6920345B2 (en) | 2003-01-24 | 2005-07-19 | Masimo Corporation | Optical sensor including disposable and reusable elements |
US7500950B2 (en) | 2003-07-25 | 2009-03-10 | Masimo Corporation | Multipurpose sensor port |
US7483729B2 (en) | 2003-11-05 | 2009-01-27 | Masimo Corporation | Pulse oximeter access apparatus and method |
EP1722676B1 (en) | 2004-03-08 | 2012-12-19 | Masimo Corporation | Physiological parameter system |
US7761127B2 (en) | 2005-03-01 | 2010-07-20 | Masimo Laboratories, Inc. | Multiple wavelength sensor substrate |
CA2604653A1 (en) | 2005-04-13 | 2006-10-19 | Glucolight Corporation | Method for data reduction and calibration of an oct-based blood glucose monitor |
US7962188B2 (en) | 2005-10-14 | 2011-06-14 | Masimo Corporation | Robust alarm system |
US8182443B1 (en) | 2006-01-17 | 2012-05-22 | Masimo Corporation | Drug administration controller |
US8219172B2 (en) | 2006-03-17 | 2012-07-10 | Glt Acquisition Corp. | System and method for creating a stable optical interface |
US7941199B2 (en) | 2006-05-15 | 2011-05-10 | Masimo Laboratories, Inc. | Sepsis monitor |
US10188348B2 (en) | 2006-06-05 | 2019-01-29 | Masimo Corporation | Parameter upgrade system |
US8457707B2 (en) | 2006-09-20 | 2013-06-04 | Masimo Corporation | Congenital heart disease monitor |
US8840549B2 (en) | 2006-09-22 | 2014-09-23 | Masimo Corporation | Modular patient monitor |
US8255026B1 (en) | 2006-10-12 | 2012-08-28 | Masimo Corporation, Inc. | Patient monitor capable of monitoring the quality of attached probes and accessories |
US8265723B1 (en) | 2006-10-12 | 2012-09-11 | Cercacor Laboratories, Inc. | Oximeter probe off indicator defining probe off space |
US9861305B1 (en) | 2006-10-12 | 2018-01-09 | Masimo Corporation | Method and apparatus for calibration to reduce coupling between signals in a measurement system |
US8280473B2 (en) | 2006-10-12 | 2012-10-02 | Masino Corporation, Inc. | Perfusion index smoother |
US9192329B2 (en) | 2006-10-12 | 2015-11-24 | Masimo Corporation | Variable mode pulse indicator |
US7880626B2 (en) | 2006-10-12 | 2011-02-01 | Masimo Corporation | System and method for monitoring the life of a physiological sensor |
US8600467B2 (en) | 2006-11-29 | 2013-12-03 | Cercacor Laboratories, Inc. | Optical sensor including disposable and reusable elements |
EP2096994B1 (en) | 2006-12-09 | 2018-10-03 | Masimo Corporation | Plethysmograph variability determination |
US8852094B2 (en) | 2006-12-22 | 2014-10-07 | Masimo Corporation | Physiological parameter system |
US8652060B2 (en) | 2007-01-20 | 2014-02-18 | Masimo Corporation | Perfusion trend indicator |
US8374665B2 (en) | 2007-04-21 | 2013-02-12 | Cercacor Laboratories, Inc. | Tissue profile wellness monitor |
US8768423B2 (en) | 2008-03-04 | 2014-07-01 | Glt Acquisition Corp. | Multispot monitoring for use in optical coherence tomography |
WO2009134724A1 (en) | 2008-05-02 | 2009-11-05 | Masimo Corporation | Monitor configuration system |
US9107625B2 (en) | 2008-05-05 | 2015-08-18 | Masimo Corporation | Pulse oximetry system with electrical decoupling circuitry |
US20100004518A1 (en) | 2008-07-03 | 2010-01-07 | Masimo Laboratories, Inc. | Heat sink for noninvasive medical sensor |
US8630691B2 (en) | 2008-08-04 | 2014-01-14 | Cercacor Laboratories, Inc. | Multi-stream sensor front ends for noninvasive measurement of blood constituents |
SE532941C2 (en) | 2008-09-15 | 2010-05-18 | Phasein Ab | Gas sampling line for breathing gases |
US8771204B2 (en) | 2008-12-30 | 2014-07-08 | Masimo Corporation | Acoustic sensor assembly |
US8588880B2 (en) | 2009-02-16 | 2013-11-19 | Masimo Corporation | Ear sensor |
US9218454B2 (en) | 2009-03-04 | 2015-12-22 | Masimo Corporation | Medical monitoring system |
US10007758B2 (en) | 2009-03-04 | 2018-06-26 | Masimo Corporation | Medical monitoring system |
US10032002B2 (en) | 2009-03-04 | 2018-07-24 | Masimo Corporation | Medical monitoring system |
US9323894B2 (en) | 2011-08-19 | 2016-04-26 | Masimo Corporation | Health care sanitation monitoring system |
US8388353B2 (en) | 2009-03-11 | 2013-03-05 | Cercacor Laboratories, Inc. | Magnetic connector |
WO2010135373A1 (en) | 2009-05-19 | 2010-11-25 | Masimo Corporation | Disposable components for reusable physiological sensor |
US8571619B2 (en) | 2009-05-20 | 2013-10-29 | Masimo Corporation | Hemoglobin display and patient treatment |
US20110208015A1 (en) | 2009-07-20 | 2011-08-25 | Masimo Corporation | Wireless patient monitoring system |
US8473020B2 (en) | 2009-07-29 | 2013-06-25 | Cercacor Laboratories, Inc. | Non-invasive physiological sensor cover |
US20110137297A1 (en) | 2009-09-17 | 2011-06-09 | Kiani Massi Joe E | Pharmacological management system |
US20110082711A1 (en) | 2009-10-06 | 2011-04-07 | Masimo Laboratories, Inc. | Personal digital assistant or organizer for monitoring glucose levels |
WO2011047216A2 (en) | 2009-10-15 | 2011-04-21 | Masimo Corporation | Physiological acoustic monitoring system |
US9848800B1 (en) | 2009-10-16 | 2017-12-26 | Masimo Corporation | Respiratory pause detector |
US9839381B1 (en) | 2009-11-24 | 2017-12-12 | Cercacor Laboratories, Inc. | Physiological measurement system with automatic wavelength adjustment |
DE112010004682T5 (en) | 2009-12-04 | 2013-03-28 | Masimo Corporation | Calibration for multi-level physiological monitors |
US9153112B1 (en) | 2009-12-21 | 2015-10-06 | Masimo Corporation | Modular patient monitor |
DE112011100282T5 (en) | 2010-01-19 | 2012-11-29 | Masimo Corporation | Wellness assessment system |
DE112011100761T5 (en) | 2010-03-01 | 2013-01-03 | Masimo Corporation | Adaptive alarm system |
WO2011112524A1 (en) | 2010-03-08 | 2011-09-15 | Masimo Corporation | Reprocessing of a physiological sensor |
US9307928B1 (en) | 2010-03-30 | 2016-04-12 | Masimo Corporation | Plethysmographic respiration processor |
US8666468B1 (en) | 2010-05-06 | 2014-03-04 | Masimo Corporation | Patient monitor for determining microcirculation state |
US9408542B1 (en) | 2010-07-22 | 2016-08-09 | Masimo Corporation | Non-invasive blood pressure measurement system |
JP5710767B2 (en) | 2010-09-28 | 2015-04-30 | マシモ コーポレイション | Depth of consciousness monitor including oximeter |
US9211095B1 (en) | 2010-10-13 | 2015-12-15 | Masimo Corporation | Physiological measurement logic engine |
US20120226117A1 (en) | 2010-12-01 | 2012-09-06 | Lamego Marcelo M | Handheld processing device including medical applications for minimally and non invasive glucose measurements |
WO2012109671A1 (en) | 2011-02-13 | 2012-08-16 | Masimo Corporation | Medical characterization system |
US9066666B2 (en) | 2011-02-25 | 2015-06-30 | Cercacor Laboratories, Inc. | Patient monitor for monitoring microcirculation |
US9986919B2 (en) | 2011-06-21 | 2018-06-05 | Masimo Corporation | Patient monitoring system |
US9532722B2 (en) | 2011-06-21 | 2017-01-03 | Masimo Corporation | Patient monitoring system |
US11439329B2 (en) | 2011-07-13 | 2022-09-13 | Masimo Corporation | Multiple measurement mode in a physiological sensor |
US9782077B2 (en) | 2011-08-17 | 2017-10-10 | Masimo Corporation | Modulated physiological sensor |
US9808188B1 (en) | 2011-10-13 | 2017-11-07 | Masimo Corporation | Robust fractional saturation determination |
US9943269B2 (en) | 2011-10-13 | 2018-04-17 | Masimo Corporation | System for displaying medical monitoring data |
WO2013056160A2 (en) | 2011-10-13 | 2013-04-18 | Masimo Corporation | Medical monitoring hub |
EP3603502B1 (en) | 2011-10-13 | 2023-10-04 | Masimo Corporation | Physiological acoustic monitoring system |
US9778079B1 (en) | 2011-10-27 | 2017-10-03 | Masimo Corporation | Physiological monitor gauge panel |
US11172890B2 (en) | 2012-01-04 | 2021-11-16 | Masimo Corporation | Automated condition screening and detection |
US9392945B2 (en) | 2012-01-04 | 2016-07-19 | Masimo Corporation | Automated CCHD screening and detection |
US10149616B2 (en) | 2012-02-09 | 2018-12-11 | Masimo Corporation | Wireless patient monitoring device |
US9195385B2 (en) | 2012-03-25 | 2015-11-24 | Masimo Corporation | Physiological monitor touchscreen interface |
JP6490577B2 (en) | 2012-04-17 | 2019-03-27 | マシモ・コーポレイション | How to operate a pulse oximeter device |
WO2013184965A1 (en) | 2012-06-07 | 2013-12-12 | Masimo Corporation | Depth of consciousness monitor |
US11478158B2 (en) | 2013-05-23 | 2022-10-25 | Medibotics Llc | Wearable ring of optical biometric sensors |
US9697928B2 (en) | 2012-08-01 | 2017-07-04 | Masimo Corporation | Automated assembly sensor cable |
US10827961B1 (en) | 2012-08-29 | 2020-11-10 | Masimo Corporation | Physiological measurement calibration |
US9955937B2 (en) | 2012-09-20 | 2018-05-01 | Masimo Corporation | Acoustic patient sensor coupler |
US9877650B2 (en) | 2012-09-20 | 2018-01-30 | Masimo Corporation | Physiological monitor with mobile computing device connectivity |
US9749232B2 (en) | 2012-09-20 | 2017-08-29 | Masimo Corporation | Intelligent medical network edge router |
US9560996B2 (en) | 2012-10-30 | 2017-02-07 | Masimo Corporation | Universal medical system |
US9787568B2 (en) | 2012-11-05 | 2017-10-10 | Cercacor Laboratories, Inc. | Physiological test credit method |
US9724025B1 (en) | 2013-01-16 | 2017-08-08 | Masimo Corporation | Active-pulse blood analysis system |
US10441181B1 (en) | 2013-03-13 | 2019-10-15 | Masimo Corporation | Acoustic pulse and respiration monitoring system |
WO2014164139A1 (en) | 2013-03-13 | 2014-10-09 | Masimo Corporation | Systems and methods for monitoring a patient health network |
US9936917B2 (en) | 2013-03-14 | 2018-04-10 | Masimo Laboratories, Inc. | Patient monitor placement indicator |
US9891079B2 (en) | 2013-07-17 | 2018-02-13 | Masimo Corporation | Pulser with double-bearing position encoder for non-invasive physiological monitoring |
WO2015020911A2 (en) | 2013-08-05 | 2015-02-12 | Cercacor Laboratories, Inc. | Blood pressure monitor with valve-chamber assembly |
WO2015038683A2 (en) | 2013-09-12 | 2015-03-19 | Cercacor Laboratories, Inc. | Medical device management system |
US10010276B2 (en) | 2013-10-07 | 2018-07-03 | Masimo Corporation | Regional oximetry user interface |
US11147518B1 (en) | 2013-10-07 | 2021-10-19 | Masimo Corporation | Regional oximetry signal processor |
US10828007B1 (en) | 2013-10-11 | 2020-11-10 | Masimo Corporation | Acoustic sensor with attachment portion |
US10832818B2 (en) | 2013-10-11 | 2020-11-10 | Masimo Corporation | Alarm notification system |
US10279247B2 (en) | 2013-12-13 | 2019-05-07 | Masimo Corporation | Avatar-incentive healthcare therapy |
US11259745B2 (en) | 2014-01-28 | 2022-03-01 | Masimo Corporation | Autonomous drug delivery system |
US10123729B2 (en) | 2014-06-13 | 2018-11-13 | Nanthealth, Inc. | Alarm fatigue management systems and methods |
US10231670B2 (en) | 2014-06-19 | 2019-03-19 | Masimo Corporation | Proximity sensor in pulse oximeter |
US10111591B2 (en) | 2014-08-26 | 2018-10-30 | Nanthealth, Inc. | Real-time monitoring systems and methods in a healthcare environment |
US10231657B2 (en) | 2014-09-04 | 2019-03-19 | Masimo Corporation | Total hemoglobin screening sensor |
US10383520B2 (en) | 2014-09-18 | 2019-08-20 | Masimo Semiconductor, Inc. | Enhanced visible near-infrared photodiode and non-invasive physiological sensor |
WO2016057553A1 (en) | 2014-10-07 | 2016-04-14 | Masimo Corporation | Modular physiological sensors |
KR102575058B1 (en) | 2015-01-23 | 2023-09-05 | 마시모 스웨덴 에이비 | Nasal/Oral Cannula Systems and Manufacturing |
KR102609605B1 (en) | 2015-02-06 | 2023-12-05 | 마시모 코오퍼레이션 | Fold flex circuit for optical probes |
US10568553B2 (en) | 2015-02-06 | 2020-02-25 | Masimo Corporation | Soft boot pulse oximetry sensor |
MX2017010045A (en) | 2015-02-06 | 2018-04-10 | Masimo Corp | Connector assembly with pogo pins for use with medical sensors. |
US10524738B2 (en) | 2015-05-04 | 2020-01-07 | Cercacor Laboratories, Inc. | Noninvasive sensor system with visual infographic display |
WO2016191307A1 (en) | 2015-05-22 | 2016-12-01 | Cercacor Laboratories, Inc. | Non-invasive optical physiological differential pathlength sensor |
US10448871B2 (en) | 2015-07-02 | 2019-10-22 | Masimo Corporation | Advanced pulse oximetry sensor |
EP3334334A1 (en) | 2015-08-11 | 2018-06-20 | Masimo Corporation | Medical monitoring analysis and replay including indicia responsive to light attenuated by body tissue |
AU2016315947B2 (en) | 2015-08-31 | 2021-02-18 | Masimo Corporation | Wireless patient monitoring systems and methods |
US11504066B1 (en) | 2015-09-04 | 2022-11-22 | Cercacor Laboratories, Inc. | Low-noise sensor system |
KR102374116B1 (en) * | 2015-09-30 | 2022-03-11 | 삼성전자주식회사 | Electronic device |
US11679579B2 (en) | 2015-12-17 | 2023-06-20 | Masimo Corporation | Varnish-coated release liner |
US10993662B2 (en) | 2016-03-04 | 2021-05-04 | Masimo Corporation | Nose sensor |
US10537285B2 (en) | 2016-03-04 | 2020-01-21 | Masimo Corporation | Nose sensor |
US11191484B2 (en) | 2016-04-29 | 2021-12-07 | Masimo Corporation | Optical sensor tape |
US10608817B2 (en) | 2016-07-06 | 2020-03-31 | Masimo Corporation | Secure and zero knowledge data sharing for cloud applications |
US10617302B2 (en) | 2016-07-07 | 2020-04-14 | Masimo Corporation | Wearable pulse oximeter and respiration monitor |
WO2018071715A1 (en) | 2016-10-13 | 2018-04-19 | Masimo Corporation | Systems and methods for patient fall detection |
US11504058B1 (en) | 2016-12-02 | 2022-11-22 | Masimo Corporation | Multi-site noninvasive measurement of a physiological parameter |
US10750984B2 (en) | 2016-12-22 | 2020-08-25 | Cercacor Laboratories, Inc. | Methods and devices for detecting intensity of light with translucent detector |
US10721785B2 (en) | 2017-01-18 | 2020-07-21 | Masimo Corporation | Patient-worn wireless physiological sensor with pairing functionality |
WO2018156804A1 (en) | 2017-02-24 | 2018-08-30 | Masimo Corporation | System for displaying medical monitoring data |
US11086609B2 (en) | 2017-02-24 | 2021-08-10 | Masimo Corporation | Medical monitoring hub |
WO2018156648A1 (en) | 2017-02-24 | 2018-08-30 | Masimo Corporation | Managing dynamic licenses for physiological parameters in a patient monitoring environment |
US10388120B2 (en) | 2017-02-24 | 2019-08-20 | Masimo Corporation | Localized projection of audible noises in medical settings |
WO2018156809A1 (en) | 2017-02-24 | 2018-08-30 | Masimo Corporation | Augmented reality system for displaying patient data |
US10327713B2 (en) | 2017-02-24 | 2019-06-25 | Masimo Corporation | Modular multi-parameter patient monitoring device |
CN110891486A (en) | 2017-03-10 | 2020-03-17 | 梅西莫股份有限公司 | Pneumonia screening instrument |
WO2018194992A1 (en) | 2017-04-18 | 2018-10-25 | Masimo Corporation | Nose sensor |
US10918281B2 (en) | 2017-04-26 | 2021-02-16 | Masimo Corporation | Medical monitoring device having multiple configurations |
USD835285S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
USD835282S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
USD835283S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
EP3614909B1 (en) | 2017-04-28 | 2024-04-03 | Masimo Corporation | Spot check measurement system |
USD835284S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
WO2018208616A1 (en) | 2017-05-08 | 2018-11-15 | Masimo Corporation | System for pairing a medical system to a network controller by use of a dongle |
JP2019015604A (en) * | 2017-07-06 | 2019-01-31 | 横河電機株式会社 | Measuring apparatus |
US11026604B2 (en) | 2017-07-13 | 2021-06-08 | Cercacor Laboratories, Inc. | Medical monitoring device for harmonizing physiological measurements |
USD906970S1 (en) | 2017-08-15 | 2021-01-05 | Masimo Corporation | Connector |
USD890708S1 (en) | 2017-08-15 | 2020-07-21 | Masimo Corporation | Connector |
US10637181B2 (en) | 2017-08-15 | 2020-04-28 | Masimo Corporation | Water resistant connector for noninvasive patient monitor |
EP4039177A1 (en) | 2017-10-19 | 2022-08-10 | Masimo Corporation | Display arrangement for medical monitoring system |
EP3703566B1 (en) | 2017-10-31 | 2023-07-26 | Masimo Corporation | System for displaying oxygen state indications |
USD925597S1 (en) | 2017-10-31 | 2021-07-20 | Masimo Corporation | Display screen or portion thereof with graphical user interface |
US11766198B2 (en) | 2018-02-02 | 2023-09-26 | Cercacor Laboratories, Inc. | Limb-worn patient monitoring device |
WO2019204368A1 (en) | 2018-04-19 | 2019-10-24 | Masimo Corporation | Mobile patient alarm display |
WO2019209915A1 (en) | 2018-04-24 | 2019-10-31 | Cercacor Laboratories, Inc. | Easy insert finger sensor for transmission based spectroscopy sensor |
EP3784130A4 (en) * | 2018-04-27 | 2022-06-01 | Hydrostasis, Inc. | Tissue hydration monitor |
US11627919B2 (en) | 2018-06-06 | 2023-04-18 | Masimo Corporation | Opioid overdose monitoring |
US10779098B2 (en) | 2018-07-10 | 2020-09-15 | Masimo Corporation | Patient monitor alarm speaker analyzer |
US11872156B2 (en) | 2018-08-22 | 2024-01-16 | Masimo Corporation | Core body temperature measurement |
USD917564S1 (en) | 2018-10-11 | 2021-04-27 | Masimo Corporation | Display screen or portion thereof with graphical user interface |
USD917550S1 (en) | 2018-10-11 | 2021-04-27 | Masimo Corporation | Display screen or portion thereof with a graphical user interface |
USD999246S1 (en) | 2018-10-11 | 2023-09-19 | Masimo Corporation | Display screen or portion thereof with a graphical user interface |
US11406286B2 (en) | 2018-10-11 | 2022-08-09 | Masimo Corporation | Patient monitoring device with improved user interface |
USD998631S1 (en) | 2018-10-11 | 2023-09-12 | Masimo Corporation | Display screen or portion thereof with a graphical user interface |
JP7128960B2 (en) | 2018-10-11 | 2022-08-31 | マシモ・コーポレイション | Patient connector assembly with vertical detent |
US11389093B2 (en) | 2018-10-11 | 2022-07-19 | Masimo Corporation | Low noise oximetry cable |
USD998630S1 (en) | 2018-10-11 | 2023-09-12 | Masimo Corporation | Display screen or portion thereof with a graphical user interface |
USD916135S1 (en) | 2018-10-11 | 2021-04-13 | Masimo Corporation | Display screen or portion thereof with a graphical user interface |
USD897098S1 (en) | 2018-10-12 | 2020-09-29 | Masimo Corporation | Card holder set |
US11464410B2 (en) | 2018-10-12 | 2022-10-11 | Masimo Corporation | Medical systems and methods |
AU2019357721A1 (en) | 2018-10-12 | 2021-05-27 | Masimo Corporation | System for transmission of sensor data using dual communication protocol |
US11684296B2 (en) | 2018-12-21 | 2023-06-27 | Cercacor Laboratories, Inc. | Noninvasive physiological sensor |
US11701043B2 (en) | 2019-04-17 | 2023-07-18 | Masimo Corporation | Blood pressure monitor attachment assembly |
USD921202S1 (en) | 2019-08-16 | 2021-06-01 | Masimo Corporation | Holder for a blood pressure device |
USD917704S1 (en) | 2019-08-16 | 2021-04-27 | Masimo Corporation | Patient monitor |
USD919094S1 (en) | 2019-08-16 | 2021-05-11 | Masimo Corporation | Blood pressure device |
USD985498S1 (en) | 2019-08-16 | 2023-05-09 | Masimo Corporation | Connector |
USD919100S1 (en) | 2019-08-16 | 2021-05-11 | Masimo Corporation | Holder for a patient monitor |
US11832940B2 (en) | 2019-08-27 | 2023-12-05 | Cercacor Laboratories, Inc. | Non-invasive medical monitoring device for blood analyte measurements |
USD927699S1 (en) | 2019-10-18 | 2021-08-10 | Masimo Corporation | Electrode pad |
KR20220083771A (en) | 2019-10-18 | 2022-06-20 | 마시모 코오퍼레이션 | Display layouts and interactive objects for patient monitoring |
CA3157995A1 (en) | 2019-10-25 | 2021-04-29 | Cercacor Laboratories, Inc. | Indicator compounds, devices comprising indicator compounds, and methods of making and using the same |
EP3920788B1 (en) | 2020-01-13 | 2023-06-07 | Masimo Corporation | Wearable device with physiological parameters monitoring |
US11879960B2 (en) | 2020-02-13 | 2024-01-23 | Masimo Corporation | System and method for monitoring clinical activities |
EP4104037A1 (en) | 2020-02-13 | 2022-12-21 | Masimo Corporation | System and method for monitoring clinical activities |
US20210290177A1 (en) | 2020-03-20 | 2021-09-23 | Masimo Corporation | Wearable device for monitoring health status |
USD933232S1 (en) | 2020-05-11 | 2021-10-12 | Masimo Corporation | Blood pressure monitor |
USD979516S1 (en) | 2020-05-11 | 2023-02-28 | Masimo Corporation | Connector |
KR20220000160A (en) * | 2020-06-25 | 2022-01-03 | 삼성전자주식회사 | Apparatus and method for analyzing substance of object |
USD974193S1 (en) | 2020-07-27 | 2023-01-03 | Masimo Corporation | Wearable temperature measurement device |
USD980091S1 (en) | 2020-07-27 | 2023-03-07 | Masimo Corporation | Wearable temperature measurement device |
USD946596S1 (en) | 2020-09-30 | 2022-03-22 | Masimo Corporation | Display screen or portion thereof with graphical user interface |
USD946597S1 (en) | 2020-09-30 | 2022-03-22 | Masimo Corporation | Display screen or portion thereof with graphical user interface |
USD946598S1 (en) | 2020-09-30 | 2022-03-22 | Masimo Corporation | Display screen or portion thereof with graphical user interface |
US11666256B2 (en) | 2020-10-27 | 2023-06-06 | Michael Edward Labrecque | Pulse oximeter sensor |
US20220146494A1 (en) * | 2020-11-10 | 2022-05-12 | GE Precision Healthcare LLC | REATTACHABLE SpO2 SENSOR WITH AMBIENT LIGHT ATTENUATION |
USD997365S1 (en) | 2021-06-24 | 2023-08-29 | Masimo Corporation | Physiological nose sensor |
KR20240032835A (en) | 2021-07-13 | 2024-03-12 | 마시모 코오퍼레이션 | Wearable device that monitors physiological indicators |
US20230058052A1 (en) | 2021-07-21 | 2023-02-23 | Masimo Corporation | Wearable band for health monitoring device |
USD1000975S1 (en) | 2021-09-22 | 2023-10-10 | Masimo Corporation | Wearable temperature measurement device |
CN113786172B (en) * | 2021-11-17 | 2022-02-22 | 深圳市脉度科技有限公司 | Physiological parameter measuring system and method |
Family Cites Families (606)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5041187A (en) | 1988-04-29 | 1991-08-20 | Thor Technology Corporation | Oximeter sensor assembly with integral cable and method of forming the same |
US4964408A (en) | 1988-04-29 | 1990-10-23 | Thor Technology Corporation | Oximeter sensor assembly with integral cable |
US5069213A (en) | 1988-04-29 | 1991-12-03 | Thor Technology Corporation | Oximeter sensor assembly with integral cable and encoder |
US5099842A (en) | 1988-10-28 | 1992-03-31 | Nellcor Incorporated | Perinatal pulse oximetry probe |
US4960128A (en) | 1988-11-14 | 1990-10-02 | Paramed Technology Incorporated | Method and apparatus for continuously and non-invasively measuring the blood pressure of a patient |
US5163438A (en) | 1988-11-14 | 1992-11-17 | Paramed Technology Incorporated | Method and apparatus for continuously and noninvasively measuring the blood pressure of a patient |
US5203329A (en) | 1989-10-05 | 1993-04-20 | Colin Electronics Co., Ltd. | Noninvasive reflectance oximeter sensor providing controlled minimum optical detection depth |
GB9006251D0 (en) | 1990-03-20 | 1990-05-16 | Payne Julian M | Monitor of physiological functions |
GB9011887D0 (en) | 1990-05-26 | 1990-07-18 | Le Fit Ltd | Pulse responsive device |
US5158091A (en) * | 1990-11-30 | 1992-10-27 | Ivac Corporation | Tonometry system for determining blood pressure |
US5228449A (en) | 1991-01-22 | 1993-07-20 | Athanasios G. Christ | System and method for detecting out-of-hospital cardiac emergencies and summoning emergency assistance |
US5319355A (en) | 1991-03-06 | 1994-06-07 | Russek Linda G | Alarm for patient monitor and life support equipment system |
US5632272A (en) | 1991-03-07 | 1997-05-27 | Masimo Corporation | Signal processing apparatus |
MX9702434A (en) | 1991-03-07 | 1998-05-31 | Masimo Corp | Signal processing apparatus. |
US5490505A (en) | 1991-03-07 | 1996-02-13 | Masimo Corporation | Signal processing apparatus |
ATE184716T1 (en) | 1991-03-07 | 1999-10-15 | Masimo Corp | DEVICE AND METHOD FOR SIGNAL PROCESSING |
US6541756B2 (en) | 1991-03-21 | 2003-04-01 | Masimo Corporation | Shielded optical probe having an electrical connector |
US6580086B1 (en) | 1999-08-26 | 2003-06-17 | Masimo Corporation | Shielded optical probe and method |
US5638818A (en) | 1991-03-21 | 1997-06-17 | Masimo Corporation | Low noise optical probe |
US5995855A (en) | 1998-02-11 | 1999-11-30 | Masimo Corporation | Pulse oximetry sensor adapter |
US5645440A (en) | 1995-10-16 | 1997-07-08 | Masimo Corporation | Patient cable connector |
US5377676A (en) | 1991-04-03 | 1995-01-03 | Cedars-Sinai Medical Center | Method for determining the biodistribution of substances using fluorescence spectroscopy |
AU667199B2 (en) | 1991-11-08 | 1996-03-14 | Physiometrix, Inc. | EEG headpiece with disposable electrodes and apparatus and system and method for use therewith |
US5353793A (en) | 1991-11-25 | 1994-10-11 | Oishi-Kogyo Company | Sensor apparatus |
FI92139C (en) | 1992-02-28 | 1994-10-10 | Matti Myllymaeki | Monitoring device for the health condition, which is attached to the wrist |
US5370114A (en) | 1992-03-12 | 1994-12-06 | Wong; Jacob Y. | Non-invasive blood chemistry measurement by stimulated infrared relaxation emission |
US6785568B2 (en) | 1992-05-18 | 2004-08-31 | Non-Invasive Technology Inc. | Transcranial examination of the brain |
WO1994012096A1 (en) * | 1992-12-01 | 1994-06-09 | Somanetics Corporation | Patient sensor for optical cerebral oximeters |
CA2140658C (en) | 1992-12-07 | 2001-07-24 | Jocelyn Durand | Electronic stethoscope |
US5497771A (en) * | 1993-04-02 | 1996-03-12 | Mipm Mammendorfer Institut Fuer Physik Und Medizin Gmbh | Apparatus for measuring the oxygen saturation of fetuses during childbirth |
US5341805A (en) | 1993-04-06 | 1994-08-30 | Cedars-Sinai Medical Center | Glucose fluorescence monitor and method |
EP1491135A3 (en) | 1993-04-12 | 2005-09-07 | Hema Metrics, Inc. | Method and apparatus for monitoring blood constituents |
US5494043A (en) | 1993-05-04 | 1996-02-27 | Vital Insite, Inc. | Arterial sensor |
USD353195S (en) | 1993-05-28 | 1994-12-06 | Gary Savage | Electronic stethoscope housing |
USD353196S (en) | 1993-05-28 | 1994-12-06 | Gary Savage | Stethoscope head |
FI932881A (en) | 1993-06-22 | 1994-12-23 | Increa Oy | Device for recording quantities associated with the blood circulation system |
US5452717A (en) | 1993-07-14 | 1995-09-26 | Masimo Corporation | Finger-cot probe |
US5337744A (en) | 1993-07-14 | 1994-08-16 | Masimo Corporation | Low noise finger cot probe |
US5456252A (en) | 1993-09-30 | 1995-10-10 | Cedars-Sinai Medical Center | Induced fluorescence spectroscopy blood perfusion and pH monitor and method |
US7376453B1 (en) | 1993-10-06 | 2008-05-20 | Masimo Corporation | Signal processing apparatus |
US5533511A (en) | 1994-01-05 | 1996-07-09 | Vital Insite, Incorporated | Apparatus and method for noninvasive blood pressure measurement |
USD359546S (en) | 1994-01-27 | 1995-06-20 | The Ratechnologies Inc. | Housing for a dental unit disinfecting device |
US5699808A (en) | 1994-02-07 | 1997-12-23 | New York University | EEG operative and post-operative patient monitoring system and method |
US6371921B1 (en) | 1994-04-15 | 2002-04-16 | Masimo Corporation | System and method of determining whether to recalibrate a blood pressure monitor |
US5590649A (en) | 1994-04-15 | 1997-01-07 | Vital Insite, Inc. | Apparatus and method for measuring an induced perturbation to determine blood pressure |
US5791347A (en) | 1994-04-15 | 1998-08-11 | Vital Insite, Inc. | Motion insensitive pulse detector |
US5810734A (en) | 1994-04-15 | 1998-09-22 | Vital Insite, Inc. | Apparatus and method for measuring an induced perturbation to determine a physiological parameter |
US5785659A (en) | 1994-04-15 | 1998-07-28 | Vital Insite, Inc. | Automatically activated blood pressure measurement device |
US5904654A (en) | 1995-10-20 | 1999-05-18 | Vital Insite, Inc. | Exciter-detector unit for measuring physiological parameters |
USD362063S (en) | 1994-04-21 | 1995-09-05 | Gary Savage | Stethoscope headset |
USD361840S (en) | 1994-04-21 | 1995-08-29 | Gary Savage | Stethoscope head |
USD363120S (en) | 1994-04-21 | 1995-10-10 | Gary Savage | Stethoscope ear tip |
US5561275A (en) | 1994-04-28 | 1996-10-01 | Delstar Services Informatiques (1993) Inc. | Headset for electronic stethoscope |
WO2004093025A1 (en) | 1994-06-28 | 2004-10-28 | Tohru Oka | Emergency call unit |
US5490523A (en) | 1994-06-29 | 1996-02-13 | Nonin Medical Inc. | Finger clip pulse oximeter |
US5462051A (en) | 1994-08-31 | 1995-10-31 | Colin Corporation | Medical communication system |
EP1905352B1 (en) | 1994-10-07 | 2014-07-16 | Masimo Corporation | Signal processing method |
US8019400B2 (en) | 1994-10-07 | 2011-09-13 | Masimo Corporation | Signal processing apparatus |
US8280682B2 (en) | 2000-12-15 | 2012-10-02 | Tvipr, Llc | Device for monitoring movement of shipped goods |
DE69627477T2 (en) | 1995-01-03 | 2004-03-18 | Non-Invasive Technology, Inc. | OPTICAL COUPLING DEVICE FOR IN-VIVO EXAMINATION OF BIOLOGICAL TISSUES |
US5562002A (en) | 1995-02-03 | 1996-10-08 | Sensidyne Inc. | Positive displacement piston flow meter with damping assembly |
WO1996027325A1 (en) | 1995-03-03 | 1996-09-12 | Huch Albert W | Device for measuring oxygen saturation in the blood present in the body |
US5623925A (en) | 1995-06-05 | 1997-04-29 | Cmed, Inc. | Virtual medical instrument for performing medical diagnostic testing on patients |
US5743262A (en) | 1995-06-07 | 1998-04-28 | Masimo Corporation | Blood glucose monitoring system |
US6931268B1 (en) | 1995-06-07 | 2005-08-16 | Masimo Laboratories, Inc. | Active pulse blood constituent monitoring |
US5760910A (en) | 1995-06-07 | 1998-06-02 | Masimo Corporation | Optical filter for spectroscopic measurement and method of producing the optical filter |
US5638816A (en) | 1995-06-07 | 1997-06-17 | Masimo Corporation | Active pulse blood constituent monitoring |
US5758644A (en) | 1995-06-07 | 1998-06-02 | Masimo Corporation | Manual and automatic probe calibration |
US6517283B2 (en) | 2001-01-16 | 2003-02-11 | Donald Edward Coffey | Cascading chute drainage system |
AU6099196A (en) | 1995-06-21 | 1997-01-22 | Minnesota Mining And Manufacturing Company | Adhesive compositions, bonding films made therefrom and processes for making bonding films |
KR100197580B1 (en) | 1995-09-13 | 1999-06-15 | 이민화 | A living body monitoring system making use of wireless netwokk |
KR970020056A (en) | 1995-09-19 | 1997-05-28 | 노보루 아까사까 | Patient monitor device |
USD393830S (en) | 1995-10-16 | 1998-04-28 | Masimo Corporation | Patient cable connector |
JP2919326B2 (en) | 1995-11-09 | 1999-07-12 | 株式会社コーポレーションミユキ | Helper system |
FI100164B (en) * | 1995-11-29 | 1997-10-15 | Instrumentarium Oy | Pulsoximätargivare |
US6232609B1 (en) | 1995-12-01 | 2001-05-15 | Cedars-Sinai Medical Center | Glucose monitoring apparatus and method using laser-induced emission spectroscopy |
US6253097B1 (en) | 1996-03-06 | 2001-06-26 | Datex-Ohmeda, Inc. | Noninvasive medical monitoring instrument using surface emitting laser devices |
JPH09257508A (en) | 1996-03-26 | 1997-10-03 | Matsushita Electric Works Ltd | Radio guide system |
US5890929A (en) | 1996-06-19 | 1999-04-06 | Masimo Corporation | Shielded medical connector |
US6027452A (en) | 1996-06-26 | 2000-02-22 | Vital Insite, Inc. | Rapid non-invasive blood pressure measuring device |
US5800349A (en) | 1996-10-15 | 1998-09-01 | Nonin Medical, Inc. | Offset pulse oximeter sensor |
US5830137A (en) | 1996-11-18 | 1998-11-03 | University Of South Florida | Green light pulse oximeter |
US6102856A (en) | 1997-02-12 | 2000-08-15 | Groff; Clarence P | Wearable vital sign monitoring system |
US6229856B1 (en) | 1997-04-14 | 2001-05-08 | Masimo Corporation | Method and apparatus for demodulating signals in a pulse oximetry system |
US5919134A (en) | 1997-04-14 | 1999-07-06 | Masimo Corp. | Method and apparatus for demodulating signals in a pulse oximetry system |
US6002952A (en) | 1997-04-14 | 1999-12-14 | Masimo Corporation | Signal processing apparatus and method |
JPH10314133A (en) | 1997-05-21 | 1998-12-02 | Teruo Ido | Biological signal radio equipment of arm mounting type |
TW357517B (en) | 1997-05-29 | 1999-05-01 | Koji Akai | Monitoring system |
US6124597A (en) | 1997-07-07 | 2000-09-26 | Cedars-Sinai Medical Center | Method and devices for laser induced fluorescence attenuation spectroscopy |
US6343223B1 (en) * | 1997-07-30 | 2002-01-29 | Mallinckrodt Inc. | Oximeter sensor with offset emitters and detector and heating device |
JPH1170086A (en) | 1997-08-29 | 1999-03-16 | Atsukusu Kk | Emergency informing system |
US6198952B1 (en) | 1998-10-30 | 2001-03-06 | Medtronic, Inc. | Multiple lens oxygen sensor for medical electrical lead |
US5987343A (en) | 1997-11-07 | 1999-11-16 | Datascope Investment Corp. | Method for storing pulse oximetry sensor characteristics |
US6184521B1 (en) | 1998-01-06 | 2001-02-06 | Masimo Corporation | Photodiode detector with integrated noise shielding |
CA2315192C (en) | 1998-01-27 | 2008-04-29 | Lightouch Medical, Inc. | Method and device for tissue modulation |
US6241683B1 (en) | 1998-02-20 | 2001-06-05 | INSTITUT DE RECHERCHES CLINIQUES DE MONTRéAL (IRCM) | Phonospirometry for non-invasive monitoring of respiration |
US6525386B1 (en) | 1998-03-10 | 2003-02-25 | Masimo Corporation | Non-protruding optoelectronic lens |
US6165005A (en) | 1998-03-19 | 2000-12-26 | Masimo Corporation | Patient cable sensor switch |
US5997343A (en) | 1998-03-19 | 1999-12-07 | Masimo Corporation | Patient cable sensor switch |
US6721582B2 (en) | 1999-04-06 | 2004-04-13 | Argose, Inc. | Non-invasive tissue glucose level monitoring |
US6505059B1 (en) | 1998-04-06 | 2003-01-07 | The General Hospital Corporation | Non-invasive tissue glucose level monitoring |
US7899518B2 (en) | 1998-04-06 | 2011-03-01 | Masimo Laboratories, Inc. | Non-invasive tissue glucose level monitoring |
US6728560B2 (en) | 1998-04-06 | 2004-04-27 | The General Hospital Corporation | Non-invasive tissue glucose level monitoring |
WO1999062399A1 (en) | 1998-06-03 | 1999-12-09 | Masimo Corporation | Stereo pulse oximeter |
CA2334964C (en) | 1998-06-11 | 2009-03-24 | Spo Medical Equipment Ltd. | Physiological stress detector device and method |
US6128521A (en) | 1998-07-10 | 2000-10-03 | Physiometrix, Inc. | Self adjusting headgear appliance using reservoir electrodes |
US6285896B1 (en) | 1998-07-13 | 2001-09-04 | Masimo Corporation | Fetal pulse oximetry sensor |
US6671526B1 (en) | 1998-07-17 | 2003-12-30 | Nihon Kohden Corporation | Probe and apparatus for determining concentration of light-absorbing materials in living tissue |
DE29816366U1 (en) | 1998-09-11 | 1998-12-10 | Cvetkovic Stevo | Device for monitoring and evaluating human body functions such as heart rate, blood pressure etc. |
US6129675A (en) | 1998-09-11 | 2000-10-10 | Jay; Gregory D. | Device and method for measuring pulsus paradoxus |
US6343224B1 (en) | 1998-10-15 | 2002-01-29 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
US6684091B2 (en) | 1998-10-15 | 2004-01-27 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage method |
US6721585B1 (en) | 1998-10-15 | 2004-04-13 | Sensidyne, Inc. | Universal modular pulse oximeter probe for use with reusable and disposable patient attachment devices |
US6144868A (en) | 1998-10-15 | 2000-11-07 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
US6321100B1 (en) | 1999-07-13 | 2001-11-20 | Sensidyne, Inc. | Reusable pulse oximeter probe with disposable liner |
US7245953B1 (en) | 1999-04-12 | 2007-07-17 | Masimo Corporation | Reusable pulse oximeter probe and disposable bandage apparatii |
USRE41912E1 (en) | 1998-10-15 | 2010-11-02 | Masimo Corporation | Reusable pulse oximeter probe and disposable bandage apparatus |
US6519487B1 (en) | 1998-10-15 | 2003-02-11 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
JP2000135202A (en) | 1998-10-30 | 2000-05-16 | Nippon Colin Co Ltd | Blood pressure moitoring device |
AUPP711998A0 (en) | 1998-11-13 | 1998-12-10 | Micromedical Industries Limited | Wrist mountable monitor |
US6463311B1 (en) | 1998-12-30 | 2002-10-08 | Masimo Corporation | Plethysmograph pulse recognition processor |
US6684090B2 (en) | 1999-01-07 | 2004-01-27 | Masimo Corporation | Pulse oximetry data confidence indicator |
US6606511B1 (en) | 1999-01-07 | 2003-08-12 | Masimo Corporation | Pulse oximetry pulse indicator |
US6770028B1 (en) | 1999-01-25 | 2004-08-03 | Masimo Corporation | Dual-mode pulse oximeter |
US6658276B2 (en) | 1999-01-25 | 2003-12-02 | Masimo Corporation | Pulse oximeter user interface |
US20020140675A1 (en) | 1999-01-25 | 2002-10-03 | Ali Ammar Al | System and method for altering a display mode based on a gravity-responsive sensor |
CA2684695C (en) | 1999-01-25 | 2012-11-06 | Masimo Corporation | Universal/upgrading pulse oximeter |
US6360114B1 (en) | 1999-03-25 | 2002-03-19 | Masimo Corporation | Pulse oximeter probe-off detector |
US6308089B1 (en) | 1999-04-14 | 2001-10-23 | O.B. Scientific, Inc. | Limited use medical probe |
JP2003502089A (en) | 1999-06-18 | 2003-01-21 | マシモ・コーポレイション | Pulse oximeter probe-off detection system |
US6301493B1 (en) | 1999-07-10 | 2001-10-09 | Physiometrix, Inc. | Reservoir electrodes for electroencephalograph headgear appliance |
US6515273B2 (en) | 1999-08-26 | 2003-02-04 | Masimo Corporation | System for indicating the expiration of the useful operating life of a pulse oximetry sensor |
US6943348B1 (en) | 1999-10-19 | 2005-09-13 | Masimo Corporation | System for detecting injection holding material |
ATE326900T1 (en) | 1999-10-27 | 2006-06-15 | Hospira Sedation Inc | MODULE FOR OBTAINING ELECTROENCEPHALOGRAPHY SIGNALS FROM A PATIENT |
US6317627B1 (en) | 1999-11-02 | 2001-11-13 | Physiometrix, Inc. | Anesthesia monitoring system based on electroencephalographic signals |
US6639668B1 (en) | 1999-11-03 | 2003-10-28 | Argose, Inc. | Asynchronous fluorescence scan |
US6542764B1 (en) | 1999-12-01 | 2003-04-01 | Masimo Corporation | Pulse oximeter monitor for expressing the urgency of the patient's condition |
US6671531B2 (en) | 1999-12-09 | 2003-12-30 | Masimo Corporation | Sensor wrap including foldable applicator |
US6950687B2 (en) | 1999-12-09 | 2005-09-27 | Masimo Corporation | Isolation and communication element for a resposable pulse oximetry sensor |
US6377829B1 (en) | 1999-12-09 | 2002-04-23 | Masimo Corporation | Resposable pulse oximetry sensor |
US6152754A (en) | 1999-12-21 | 2000-11-28 | Masimo Corporation | Circuit board based cable connector |
US7171251B2 (en) | 2000-02-01 | 2007-01-30 | Spo Medical Equipment Ltd. | Physiological stress detector device and system |
US20010034477A1 (en) | 2000-02-18 | 2001-10-25 | James Mansfield | Multivariate analysis of green to ultraviolet spectra of cell and tissue samples |
EP1257192A1 (en) | 2000-02-18 | 2002-11-20 | Argose, Inc. | Generation of spatially-averaged excitation-emission map in heterogeneous tissue |
US6356203B1 (en) | 2000-04-04 | 2002-03-12 | Ilife Systems, Inc. | Apparatus and method for detecting a rotational movement of a body |
US6430525B1 (en) | 2000-06-05 | 2002-08-06 | Masimo Corporation | Variable mode averager |
US6470199B1 (en) | 2000-06-21 | 2002-10-22 | Masimo Corporation | Elastic sock for positioning an optical probe |
US6697656B1 (en) | 2000-06-27 | 2004-02-24 | Masimo Corporation | Pulse oximetry sensor compatible with multiple pulse oximetry systems |
US6640116B2 (en) | 2000-08-18 | 2003-10-28 | Masimo Corporation | Optical spectroscopy pathlength measurement system |
DE60139128D1 (en) | 2000-08-18 | 2009-08-13 | Masimo Corp | PULSE OXIMETER WITH TWO OPERATING MODES |
US6368283B1 (en) | 2000-09-08 | 2002-04-09 | Institut De Recherches Cliniques De Montreal | Method and apparatus for estimating systolic and mean pulmonary artery pressures of a patient |
IL138884A (en) | 2000-10-05 | 2006-07-05 | Conmed Corp | Pulse oximeter and a method of its operation |
EP1217573A1 (en) * | 2000-12-22 | 2002-06-26 | Fingerpin AG | Device for capturing finger papillary ridges |
US6760607B2 (en) | 2000-12-29 | 2004-07-06 | Masimo Corporation | Ribbon cable substrate pulse oximetry sensor |
JP2004532526A (en) | 2001-05-03 | 2004-10-21 | マシモ・コーポレイション | Flex circuit shield optical sensor and method of manufacturing the flex circuit shield optical sensor |
US6801798B2 (en) | 2001-06-20 | 2004-10-05 | Purdue Research Foundation | Body-member-illuminating pressure cuff for use in optical noninvasive measurement of blood parameters |
US6850787B2 (en) | 2001-06-29 | 2005-02-01 | Masimo Laboratories, Inc. | Signal component processor |
US6697658B2 (en) | 2001-07-02 | 2004-02-24 | Masimo Corporation | Low power pulse oximeter |
US6595316B2 (en) | 2001-07-18 | 2003-07-22 | Andromed, Inc. | Tension-adjustable mechanism for stethoscope earpieces |
US6934570B2 (en) | 2002-01-08 | 2005-08-23 | Masimo Corporation | Physiological sensor combination |
US7355512B1 (en) | 2002-01-24 | 2008-04-08 | Masimo Corporation | Parallel alarm processor |
US6822564B2 (en) | 2002-01-24 | 2004-11-23 | Masimo Corporation | Parallel measurement alarm processor |
US7015451B2 (en) | 2002-01-25 | 2006-03-21 | Masimo Corporation | Power supply rail controller |
US6961598B2 (en) | 2002-02-22 | 2005-11-01 | Masimo Corporation | Pulse and active pulse spectraphotometry |
US7509494B2 (en) | 2002-03-01 | 2009-03-24 | Masimo Corporation | Interface cable |
US8504128B2 (en) | 2002-03-08 | 2013-08-06 | Glt Acquisition Corp. | Method and apparatus for coupling a channeled sample probe to tissue |
US8718738B2 (en) | 2002-03-08 | 2014-05-06 | Glt Acquisition Corp. | Method and apparatus for coupling a sample probe with a sample site |
US6831266B2 (en) | 2002-03-13 | 2004-12-14 | Phone-Or Ltd. | Optical transducers of high sensitivity |
US6850788B2 (en) | 2002-03-25 | 2005-02-01 | Masimo Corporation | Physiological measurement communications adapter |
US6661161B1 (en) | 2002-06-27 | 2003-12-09 | Andromed Inc. | Piezoelectric biological sound monitor with printed circuit board |
US7096054B2 (en) | 2002-08-01 | 2006-08-22 | Masimo Corporation | Low noise optical housing |
FI116097B (en) | 2002-08-21 | 2005-09-15 | Heikki Ruotoistenmaeki | Force or pressure sensor and method for its application |
US7341559B2 (en) | 2002-09-14 | 2008-03-11 | Masimo Corporation | Pulse oximetry ear sensor |
US7274955B2 (en) | 2002-09-25 | 2007-09-25 | Masimo Corporation | Parameter compensated pulse oximeter |
US7142901B2 (en) | 2002-09-25 | 2006-11-28 | Masimo Corporation | Parameter compensated physiological monitor |
US7096052B2 (en) | 2002-10-04 | 2006-08-22 | Masimo Corporation | Optical probe including predetermined emission wavelength based on patient type |
WO2004044557A2 (en) | 2002-11-12 | 2004-05-27 | Argose, Inc. | Non-invasive measurement of analytes |
WO2004047631A2 (en) | 2002-11-22 | 2004-06-10 | Masimo Laboratories, Inc. | Blood parameter measurement system |
US6970792B1 (en) | 2002-12-04 | 2005-11-29 | Masimo Laboratories, Inc. | Systems and methods for determining blood oxygen saturation values using complex number encoding |
US7919713B2 (en) | 2007-04-16 | 2011-04-05 | Masimo Corporation | Low noise oximetry cable including conductive cords |
US7225006B2 (en) | 2003-01-23 | 2007-05-29 | Masimo Corporation | Attachment and optical probe |
US6920345B2 (en) | 2003-01-24 | 2005-07-19 | Masimo Corporation | Optical sensor including disposable and reusable elements |
WO2004083820A2 (en) * | 2003-03-19 | 2004-09-30 | Trustees Of Boston University | Resonant cavity biosensor |
DK1620714T3 (en) | 2003-04-15 | 2014-03-31 | Senseonics Inc | SYSTEM AND PROCEDURE TO IMPROVE THE EFFECT OF SURFACE LIGHT ON AN OPTICAL SENSOR |
JP4551998B2 (en) | 2003-04-23 | 2010-09-29 | オータックス株式会社 | Optical probe and measurement system using the same |
CH696516A5 (en) * | 2003-05-21 | 2007-07-31 | Asulab Sa | Portable instrument for measuring a physiological quantity comprising a device for illuminating the surface of an organic tissue. |
US7003338B2 (en) | 2003-07-08 | 2006-02-21 | Masimo Corporation | Method and apparatus for reducing coupling between signals |
WO2005007215A2 (en) | 2003-07-09 | 2005-01-27 | Glucolight Corporation | Method and apparatus for tissue oximetry |
DE10333075B4 (en) | 2003-07-21 | 2011-06-16 | Siemens Ag | Method and device for training adjustment in sports, especially in running |
US7500950B2 (en) | 2003-07-25 | 2009-03-10 | Masimo Corporation | Multipurpose sensor port |
US7601123B2 (en) | 2003-08-22 | 2009-10-13 | Eppcor, Inc. | Non-invasive blood pressure monitoring device and methods |
US7254431B2 (en) | 2003-08-28 | 2007-08-07 | Masimo Corporation | Physiological parameter tracking system |
US7254434B2 (en) | 2003-10-14 | 2007-08-07 | Masimo Corporation | Variable pressure reusable sensor |
US7483729B2 (en) | 2003-11-05 | 2009-01-27 | Masimo Corporation | Pulse oximeter access apparatus and method |
US7373193B2 (en) | 2003-11-07 | 2008-05-13 | Masimo Corporation | Pulse oximetry data capture system |
US8029765B2 (en) | 2003-12-24 | 2011-10-04 | Masimo Laboratories, Inc. | SMMR (small molecule metabolite reporters) for use as in vivo glucose biosensors |
US7280858B2 (en) | 2004-01-05 | 2007-10-09 | Masimo Corporation | Pulse oximetry sensor |
US7510849B2 (en) | 2004-01-29 | 2009-03-31 | Glucolight Corporation | OCT based method for diagnosis and therapy |
US7371981B2 (en) | 2004-02-20 | 2008-05-13 | Masimo Corporation | Connector switch |
US7438683B2 (en) | 2004-03-04 | 2008-10-21 | Masimo Corporation | Application identification sensor |
US20050195094A1 (en) | 2004-03-05 | 2005-09-08 | White Russell W. | System and method for utilizing a bicycle computer to monitor athletic performance |
EP1722676B1 (en) | 2004-03-08 | 2012-12-19 | Masimo Corporation | Physiological parameter system |
US7292883B2 (en) | 2004-03-31 | 2007-11-06 | Masimo Corporation | Physiological assessment system |
CA2464029A1 (en) | 2004-04-08 | 2005-10-08 | Valery Telfort | Non-invasive ventilation monitor |
CA2464634A1 (en) | 2004-04-16 | 2005-10-16 | Andromed Inc. | Pap estimator |
US8868147B2 (en) | 2004-04-28 | 2014-10-21 | Glt Acquisition Corp. | Method and apparatus for controlling positioning of a noninvasive analyzer sample probe |
JP4515148B2 (en) | 2004-05-17 | 2010-07-28 | セイコーインスツル株式会社 | Biological information measuring apparatus and biological information measuring method |
US9341565B2 (en) | 2004-07-07 | 2016-05-17 | Masimo Corporation | Multiple-wavelength physiological monitor |
US7343186B2 (en) | 2004-07-07 | 2008-03-11 | Masimo Laboratories, Inc. | Multi-wavelength physiological monitor |
US7937128B2 (en) | 2004-07-09 | 2011-05-03 | Masimo Corporation | Cyanotic infant sensor |
US7572508B2 (en) | 2004-07-12 | 2009-08-11 | Acushnet Company | Polyurea coatings for golf equipment |
US8036727B2 (en) | 2004-08-11 | 2011-10-11 | Glt Acquisition Corp. | Methods for noninvasively measuring analyte levels in a subject |
US7254429B2 (en) | 2004-08-11 | 2007-08-07 | Glucolight Corporation | Method and apparatus for monitoring glucose levels in a biological tissue |
US7976472B2 (en) | 2004-09-07 | 2011-07-12 | Masimo Corporation | Noninvasive hypovolemia monitor |
USD566282S1 (en) | 2005-02-18 | 2008-04-08 | Masimo Corporation | Stand for a portable patient monitor |
USD554263S1 (en) | 2005-02-18 | 2007-10-30 | Masimo Corporation | Portable patient monitor |
US20060189871A1 (en) | 2005-02-18 | 2006-08-24 | Ammar Al-Ali | Portable patient monitor |
US7761127B2 (en) | 2005-03-01 | 2010-07-20 | Masimo Laboratories, Inc. | Multiple wavelength sensor substrate |
US7937129B2 (en) | 2005-03-21 | 2011-05-03 | Masimo Corporation | Variable aperture sensor |
CA2604653A1 (en) | 2005-04-13 | 2006-10-19 | Glucolight Corporation | Method for data reduction and calibration of an oct-based blood glucose monitor |
US7308292B2 (en) | 2005-04-15 | 2007-12-11 | Sensors For Medicine And Science, Inc. | Optical-based sensing devices |
US7740588B1 (en) | 2005-06-24 | 2010-06-22 | Michael Sciarra | Wireless respiratory and heart rate monitoring system |
US7899510B2 (en) | 2005-09-29 | 2011-03-01 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7962188B2 (en) | 2005-10-14 | 2011-06-14 | Masimo Corporation | Robust alarm system |
US7530942B1 (en) | 2005-10-18 | 2009-05-12 | Masimo Corporation | Remote sensing infant warmer |
WO2007064984A2 (en) | 2005-11-29 | 2007-06-07 | Masimo Corporation | Optical sensor including disposable and reusable elements |
US7990382B2 (en) | 2006-01-03 | 2011-08-02 | Masimo Corporation | Virtual display |
US8838210B2 (en) | 2006-06-29 | 2014-09-16 | AccuView, Inc. | Scanned laser vein contrast enhancer using a single laser |
US8182443B1 (en) | 2006-01-17 | 2012-05-22 | Masimo Corporation | Drug administration controller |
US8219172B2 (en) | 2006-03-17 | 2012-07-10 | Glt Acquisition Corp. | System and method for creating a stable optical interface |
GB0607270D0 (en) | 2006-04-11 | 2006-05-17 | Univ Nottingham | The pulsing blood supply |
US9176141B2 (en) | 2006-05-15 | 2015-11-03 | Cercacor Laboratories, Inc. | Physiological monitor calibration system |
US8998809B2 (en) | 2006-05-15 | 2015-04-07 | Cercacor Laboratories, Inc. | Systems and methods for calibrating minimally invasive and non-invasive physiological sensor devices |
US7941199B2 (en) | 2006-05-15 | 2011-05-10 | Masimo Laboratories, Inc. | Sepsis monitor |
US8028701B2 (en) | 2006-05-31 | 2011-10-04 | Masimo Corporation | Respiratory monitoring |
US10188348B2 (en) | 2006-06-05 | 2019-01-29 | Masimo Corporation | Parameter upgrade system |
US8457707B2 (en) | 2006-09-20 | 2013-06-04 | Masimo Corporation | Congenital heart disease monitor |
USD609193S1 (en) | 2007-10-12 | 2010-02-02 | Masimo Corporation | Connector assembly |
US8315683B2 (en) | 2006-09-20 | 2012-11-20 | Masimo Corporation | Duo connector patient cable |
USD587657S1 (en) | 2007-10-12 | 2009-03-03 | Masimo Corporation | Connector assembly |
USD614305S1 (en) | 2008-02-29 | 2010-04-20 | Masimo Corporation | Connector assembly |
US9161696B2 (en) | 2006-09-22 | 2015-10-20 | Masimo Corporation | Modular patient monitor |
US8840549B2 (en) | 2006-09-22 | 2014-09-23 | Masimo Corporation | Modular patient monitor |
US7869849B2 (en) | 2006-09-26 | 2011-01-11 | Nellcor Puritan Bennett Llc | Opaque, electrically nonconductive region on a medical sensor |
US8280473B2 (en) | 2006-10-12 | 2012-10-02 | Masino Corporation, Inc. | Perfusion index smoother |
US8255026B1 (en) | 2006-10-12 | 2012-08-28 | Masimo Corporation, Inc. | Patient monitor capable of monitoring the quality of attached probes and accessories |
US7880626B2 (en) | 2006-10-12 | 2011-02-01 | Masimo Corporation | System and method for monitoring the life of a physiological sensor |
US9861305B1 (en) | 2006-10-12 | 2018-01-09 | Masimo Corporation | Method and apparatus for calibration to reduce coupling between signals in a measurement system |
US9192329B2 (en) | 2006-10-12 | 2015-11-24 | Masimo Corporation | Variable mode pulse indicator |
US8265723B1 (en) | 2006-10-12 | 2012-09-11 | Cercacor Laboratories, Inc. | Oximeter probe off indicator defining probe off space |
US8600467B2 (en) | 2006-11-29 | 2013-12-03 | Cercacor Laboratories, Inc. | Optical sensor including disposable and reusable elements |
EP2096994B1 (en) | 2006-12-09 | 2018-10-03 | Masimo Corporation | Plethysmograph variability determination |
US7791155B2 (en) | 2006-12-22 | 2010-09-07 | Masimo Laboratories, Inc. | Detector shield |
US8852094B2 (en) | 2006-12-22 | 2014-10-07 | Masimo Corporation | Physiological parameter system |
US8652060B2 (en) | 2007-01-20 | 2014-02-18 | Masimo Corporation | Perfusion trend indicator |
FR2912049A1 (en) | 2007-02-06 | 2008-08-08 | Univ Rennes I Etablissement Pu | Physiological parameter e.g. respiration rate, measuring device i.e. wrist strap, for e.g. infant, has wedging unit including protuberance whose shape is defined in manner to cooperate with wrist to limit maintaining wrist strap rotation |
US8090432B2 (en) | 2007-02-28 | 2012-01-03 | Medtronic, Inc. | Implantable tissue perfusion sensing system and method |
US8280469B2 (en) | 2007-03-09 | 2012-10-02 | Nellcor Puritan Bennett Llc | Method for detection of aberrant tissue spectra |
GB0705033D0 (en) | 2007-03-15 | 2007-04-25 | Imp Innovations Ltd | Heart rate measurement |
EP2139383B1 (en) | 2007-03-27 | 2013-02-13 | Masimo Laboratories, Inc. | Multiple wavelength optical sensor |
US8374665B2 (en) | 2007-04-21 | 2013-02-12 | Cercacor Laboratories, Inc. | Tissue profile wellness monitor |
KR100822672B1 (en) | 2007-06-27 | 2008-04-17 | (주)실리콘화일 | Diagnosis device using image sensor and method of manufacturing the diagnosis device |
US8764671B2 (en) | 2007-06-28 | 2014-07-01 | Masimo Corporation | Disposable active pulse sensor |
US8048040B2 (en) | 2007-09-13 | 2011-11-01 | Masimo Corporation | Fluid titration system |
US8274360B2 (en) | 2007-10-12 | 2012-09-25 | Masimo Corporation | Systems and methods for storing, analyzing, and retrieving medical data |
US8310336B2 (en) | 2008-10-10 | 2012-11-13 | Masimo Corporation | Systems and methods for storing, analyzing, retrieving and displaying streaming medical data |
JP5296793B2 (en) | 2007-10-12 | 2013-09-25 | マシモ コーポレイション | Connector assembly |
US8355766B2 (en) | 2007-10-12 | 2013-01-15 | Masimo Corporation | Ceramic emitter substrate |
US8655004B2 (en) | 2007-10-16 | 2014-02-18 | Apple Inc. | Sports monitoring system for headphones, earbuds and/or headsets |
US20090247984A1 (en) | 2007-10-24 | 2009-10-01 | Masimo Laboratories, Inc. | Use of microneedles for small molecule metabolite reporter delivery |
JP2009106373A (en) * | 2007-10-26 | 2009-05-21 | Panasonic Electric Works Co Ltd | Sensing apparatus for biological surface tissue |
US8452364B2 (en) | 2007-12-28 | 2013-05-28 | Covidien LLP | System and method for attaching a sensor to a patient's skin |
US8979762B2 (en) | 2008-01-07 | 2015-03-17 | Well Being Digital Limited | Method of determining body parameters during exercise |
FI121453B (en) | 2008-02-26 | 2010-11-30 | Finsor Oy | Detection of heart rate |
US8768423B2 (en) | 2008-03-04 | 2014-07-01 | Glt Acquisition Corp. | Multispot monitoring for use in optical coherence tomography |
US8229532B2 (en) | 2008-05-02 | 2012-07-24 | The Regents Of The University Of California | External ear-placed non-invasive physiological sensor |
WO2009134724A1 (en) | 2008-05-02 | 2009-11-05 | Masimo Corporation | Monitor configuration system |
US9107625B2 (en) | 2008-05-05 | 2015-08-18 | Masimo Corporation | Pulse oximetry system with electrical decoupling circuitry |
JP5031894B2 (en) | 2008-05-12 | 2012-09-26 | パイオニア株式会社 | Self-luminous sensor device |
US8071935B2 (en) | 2008-06-30 | 2011-12-06 | Nellcor Puritan Bennett Llc | Optical detector with an overmolded faraday shield |
USD621516S1 (en) | 2008-08-25 | 2010-08-10 | Masimo Laboratories, Inc. | Patient monitoring sensor |
USD606659S1 (en) | 2008-08-25 | 2009-12-22 | Masimo Laboratories, Inc. | Patient monitor |
US20100004518A1 (en) | 2008-07-03 | 2010-01-07 | Masimo Laboratories, Inc. | Heat sink for noninvasive medical sensor |
US8203438B2 (en) | 2008-07-29 | 2012-06-19 | Masimo Corporation | Alarm suspend system |
US10080499B2 (en) | 2008-07-30 | 2018-09-25 | Medtronic, Inc. | Implantable medical system including multiple sensing modules |
US8630691B2 (en) | 2008-08-04 | 2014-01-14 | Cercacor Laboratories, Inc. | Multi-stream sensor front ends for noninvasive measurement of blood constituents |
SE532941C2 (en) | 2008-09-15 | 2010-05-18 | Phasein Ab | Gas sampling line for breathing gases |
US8911377B2 (en) | 2008-09-15 | 2014-12-16 | Masimo Corporation | Patient monitor including multi-parameter graphical display |
US8346330B2 (en) | 2008-10-13 | 2013-01-01 | Masimo Corporation | Reflection-detector sensor position indicator |
US8401602B2 (en) | 2008-10-13 | 2013-03-19 | Masimo Corporation | Secondary-emitter sensor position indicator |
US8615290B2 (en) | 2008-11-05 | 2013-12-24 | Apple Inc. | Seamlessly embedded heart rate monitor |
JP2010136921A (en) | 2008-12-12 | 2010-06-24 | Seiko Epson Corp | Measuring apparatus |
US8771204B2 (en) | 2008-12-30 | 2014-07-08 | Masimo Corporation | Acoustic sensor assembly |
US9067096B2 (en) | 2009-01-30 | 2015-06-30 | Apple Inc. | Systems and methods for providing automated workout reminders |
US8364389B2 (en) | 2009-02-02 | 2013-01-29 | Apple Inc. | Systems and methods for integrating a portable electronic device with a bicycle |
KR20100091592A (en) | 2009-02-11 | 2010-08-19 | 주식회사 엘바이오 | Pulse wave measuring apparatus capable of wearing on a wrist |
US8588880B2 (en) | 2009-02-16 | 2013-11-19 | Masimo Corporation | Ear sensor |
US8289130B2 (en) | 2009-02-19 | 2012-10-16 | Apple Inc. | Systems and methods for identifying unauthorized users of an electronic device |
JP5789199B2 (en) | 2009-02-25 | 2015-10-07 | ヴァレンセル,インコーポレイテッド | Headset and earbud |
US9323894B2 (en) | 2011-08-19 | 2016-04-26 | Masimo Corporation | Health care sanitation monitoring system |
US10007758B2 (en) | 2009-03-04 | 2018-06-26 | Masimo Corporation | Medical monitoring system |
US9218454B2 (en) | 2009-03-04 | 2015-12-22 | Masimo Corporation | Medical monitoring system |
US10032002B2 (en) | 2009-03-04 | 2018-07-24 | Masimo Corporation | Medical monitoring system |
US8388353B2 (en) | 2009-03-11 | 2013-03-05 | Cercacor Laboratories, Inc. | Magnetic connector |
US8897847B2 (en) | 2009-03-23 | 2014-11-25 | Masimo Corporation | Digit gauge for noninvasive optical sensor |
US8515515B2 (en) | 2009-03-25 | 2013-08-20 | Covidien Lp | Medical sensor with compressible light barrier and technique for using the same |
WO2010135373A1 (en) | 2009-05-19 | 2010-11-25 | Masimo Corporation | Disposable components for reusable physiological sensor |
US8571619B2 (en) | 2009-05-20 | 2013-10-29 | Masimo Corporation | Hemoglobin display and patient treatment |
CN101564290B (en) | 2009-06-10 | 2011-05-25 | 华中科技大学 | Optical multi-parameter physiology monitoring instrument |
US8418524B2 (en) | 2009-06-12 | 2013-04-16 | Masimo Corporation | Non-invasive sensor calibration device |
US8670811B2 (en) | 2009-06-30 | 2014-03-11 | Masimo Corporation | Pulse oximetry system for adjusting medical ventilation |
JP5056867B2 (en) * | 2009-07-01 | 2012-10-24 | カシオ計算機株式会社 | Biological information detection apparatus and biological information detection method |
US20110208015A1 (en) | 2009-07-20 | 2011-08-25 | Masimo Corporation | Wireless patient monitoring system |
US8471713B2 (en) | 2009-07-24 | 2013-06-25 | Cercacor Laboratories, Inc. | Interference detector for patient monitor |
US8473020B2 (en) | 2009-07-29 | 2013-06-25 | Cercacor Laboratories, Inc. | Non-invasive physiological sensor cover |
US20110028806A1 (en) | 2009-07-29 | 2011-02-03 | Sean Merritt | Reflectance calibration of fluorescence-based glucose measurements |
US8688183B2 (en) | 2009-09-03 | 2014-04-01 | Ceracor Laboratories, Inc. | Emitter driver for noninvasive patient monitor |
EP2292141B1 (en) | 2009-09-03 | 2015-06-17 | The Swatch Group Research and Development Ltd | Method and device for taking a patient's pulse using light waves with two wavelengths |
US20110172498A1 (en) | 2009-09-14 | 2011-07-14 | Olsen Gregory A | Spot check monitor credit system |
US9579039B2 (en) | 2011-01-10 | 2017-02-28 | Masimo Corporation | Non-invasive intravascular volume index monitor |
WO2011035070A1 (en) | 2009-09-17 | 2011-03-24 | Masimo Laboratories, Inc. | Improving analyte monitoring using one or more accelerometers |
US20110137297A1 (en) | 2009-09-17 | 2011-06-09 | Kiani Massi Joe E | Pharmacological management system |
US8571618B1 (en) | 2009-09-28 | 2013-10-29 | Cercacor Laboratories, Inc. | Adaptive calibration system for spectrophotometric measurements |
US20110082711A1 (en) | 2009-10-06 | 2011-04-07 | Masimo Laboratories, Inc. | Personal digital assistant or organizer for monitoring glucose levels |
RU2550427C2 (en) | 2009-10-06 | 2015-05-10 | Конинклейке Филипс Электроникс Н.В. | Method and system for performing photoplethysmography |
FR2951283B1 (en) | 2009-10-08 | 2013-02-15 | Commissariat Energie Atomique | METHOD AND DEVICE FOR DIFFUSED EXCITATION IN IMAGING |
WO2011047216A2 (en) | 2009-10-15 | 2011-04-21 | Masimo Corporation | Physiological acoustic monitoring system |
EP2488106B1 (en) | 2009-10-15 | 2020-07-08 | Masimo Corporation | Acoustic respiratory monitoring sensor having multiple sensing elements |
US8790268B2 (en) | 2009-10-15 | 2014-07-29 | Masimo Corporation | Bidirectional physiological information display |
US10463340B2 (en) | 2009-10-15 | 2019-11-05 | Masimo Corporation | Acoustic respiratory monitoring systems and methods |
US9066680B1 (en) | 2009-10-15 | 2015-06-30 | Masimo Corporation | System for determining confidence in respiratory rate measurements |
WO2011047211A1 (en) | 2009-10-15 | 2011-04-21 | Masimo Corporation | Pulse oximetry system with low noise cable hub |
US9848800B1 (en) | 2009-10-16 | 2017-12-26 | Masimo Corporation | Respiratory pause detector |
US9839381B1 (en) | 2009-11-24 | 2017-12-12 | Cercacor Laboratories, Inc. | Physiological measurement system with automatic wavelength adjustment |
DE112010004682T5 (en) | 2009-12-04 | 2013-03-28 | Masimo Corporation | Calibration for multi-level physiological monitors |
US9153112B1 (en) | 2009-12-21 | 2015-10-06 | Masimo Corporation | Modular patient monitor |
BR112012017166A2 (en) * | 2009-12-23 | 2016-03-15 | Delta Dansk Elektronik Lys Og Akustik | monitoring device |
DE112011100282T5 (en) | 2010-01-19 | 2012-11-29 | Masimo Corporation | Wellness assessment system |
US9363905B2 (en) | 2010-02-02 | 2016-06-07 | Apple Inc. | Cosmetic co-removal of material for electronic device surfaces |
DE112011100761T5 (en) | 2010-03-01 | 2013-01-03 | Masimo Corporation | Adaptive alarm system |
WO2011112524A1 (en) | 2010-03-08 | 2011-09-15 | Masimo Corporation | Reprocessing of a physiological sensor |
US9307928B1 (en) | 2010-03-30 | 2016-04-12 | Masimo Corporation | Plethysmographic respiration processor |
FI20105335A0 (en) | 2010-03-31 | 2010-03-31 | Polar Electro Oy | Heart rate detection |
US9138180B1 (en) | 2010-05-03 | 2015-09-22 | Masimo Corporation | Sensor adapter cable |
US8712494B1 (en) | 2010-05-03 | 2014-04-29 | Masimo Corporation | Reflective non-invasive sensor |
US8666468B1 (en) | 2010-05-06 | 2014-03-04 | Masimo Corporation | Patient monitor for determining microcirculation state |
US8852994B2 (en) | 2010-05-24 | 2014-10-07 | Masimo Semiconductor, Inc. | Method of fabricating bifacial tandem solar cells |
US9326712B1 (en) | 2010-06-02 | 2016-05-03 | Masimo Corporation | Opticoustic sensor |
US8740792B1 (en) | 2010-07-12 | 2014-06-03 | Masimo Corporation | Patient monitor capable of accounting for environmental conditions |
US9408542B1 (en) | 2010-07-22 | 2016-08-09 | Masimo Corporation | Non-invasive blood pressure measurement system |
WO2012027613A1 (en) | 2010-08-26 | 2012-03-01 | Masimo Corporation | Blood pressure measurement system |
US8455290B2 (en) | 2010-09-04 | 2013-06-04 | Masimo Semiconductor, Inc. | Method of fabricating epitaxial structures |
US8760517B2 (en) | 2010-09-27 | 2014-06-24 | Apple Inc. | Polarized images for security |
US9775545B2 (en) | 2010-09-28 | 2017-10-03 | Masimo Corporation | Magnetic electrical connector for patient monitors |
JP5710767B2 (en) | 2010-09-28 | 2015-04-30 | マシモ コーポレイション | Depth of consciousness monitor including oximeter |
US9241635B2 (en) | 2010-09-30 | 2016-01-26 | Fitbit, Inc. | Portable monitoring devices for processing applications and processing analysis of physiological conditions of a user associated with the portable monitoring device |
US20120165629A1 (en) | 2010-09-30 | 2012-06-28 | Sean Merritt | Systems and methods of monitoring a patient through frequency-domain photo migration spectroscopy |
US9211095B1 (en) | 2010-10-13 | 2015-12-15 | Masimo Corporation | Physiological measurement logic engine |
US8723677B1 (en) | 2010-10-20 | 2014-05-13 | Masimo Corporation | Patient safety system with automatically adjusting bed |
US9081889B2 (en) | 2010-11-10 | 2015-07-14 | Apple Inc. | Supporting the monitoring of a physical activity |
US20120226117A1 (en) | 2010-12-01 | 2012-09-06 | Lamego Marcelo M | Handheld processing device including medical applications for minimally and non invasive glucose measurements |
US20120150052A1 (en) | 2010-12-13 | 2012-06-14 | James Buchheim | Heart rate monitor |
US20120209084A1 (en) | 2011-01-21 | 2012-08-16 | Masimo Corporation | Respiratory event alert system |
US8888701B2 (en) | 2011-01-27 | 2014-11-18 | Valencell, Inc. | Apparatus and methods for monitoring physiological data during environmental interference |
WO2012109671A1 (en) | 2011-02-13 | 2012-08-16 | Masimo Corporation | Medical characterization system |
US9066666B2 (en) | 2011-02-25 | 2015-06-30 | Cercacor Laboratories, Inc. | Patient monitor for monitoring microcirculation |
US8768426B2 (en) | 2011-03-31 | 2014-07-01 | Covidien Lp | Y-shaped ear sensor with strain relief |
US8830449B1 (en) | 2011-04-18 | 2014-09-09 | Cercacor Laboratories, Inc. | Blood analysis system |
EP2699161A1 (en) | 2011-04-18 | 2014-02-26 | Cercacor Laboratories, Inc. | Pediatric monitor sensor steady game |
US9095316B2 (en) | 2011-04-20 | 2015-08-04 | Masimo Corporation | System for generating alarms based on alarm patterns |
WO2012154701A1 (en) | 2011-05-06 | 2012-11-15 | The General Hospital Corporation | System and method for tracking brain states during administration of anesthesia |
US9622692B2 (en) | 2011-05-16 | 2017-04-18 | Masimo Corporation | Personal health device |
JP2014516678A (en) | 2011-05-17 | 2014-07-17 | ライオンズゲイト テクノロジーズ,インコーポレイテッド | System and method for determining physiological characteristics of a patient using pulse oximetry |
US9532722B2 (en) | 2011-06-21 | 2017-01-03 | Masimo Corporation | Patient monitoring system |
US9986919B2 (en) | 2011-06-21 | 2018-06-05 | Masimo Corporation | Patient monitoring system |
US9245668B1 (en) | 2011-06-29 | 2016-01-26 | Cercacor Laboratories, Inc. | Low noise cable providing communication between electronic sensor components and patient monitor |
US11439329B2 (en) | 2011-07-13 | 2022-09-13 | Masimo Corporation | Multiple measurement mode in a physiological sensor |
US20130023775A1 (en) | 2011-07-20 | 2013-01-24 | Cercacor Laboratories, Inc. | Magnetic Reusable Sensor |
US9192351B1 (en) | 2011-07-22 | 2015-11-24 | Masimo Corporation | Acoustic respiratory monitoring sensor with probe-off detection |
US8755872B1 (en) | 2011-07-28 | 2014-06-17 | Masimo Corporation | Patient monitoring system for indicating an abnormal condition |
WO2013019991A1 (en) | 2011-08-04 | 2013-02-07 | Masimo Corporation | Occlusive non-inflatable blood pressure device |
US20130096405A1 (en) | 2011-08-12 | 2013-04-18 | Masimo Corporation | Fingertip pulse oximeter |
US9782077B2 (en) | 2011-08-17 | 2017-10-10 | Masimo Corporation | Modulated physiological sensor |
GB2494622A (en) | 2011-08-30 | 2013-03-20 | Oxitone Medical Ltd | Wearable pulse oximetry device |
BR112014004491A2 (en) | 2011-09-02 | 2017-03-14 | Koninklijke Philips Nv | camera and method for generating a biometric signal of a living being |
TWI486147B (en) | 2011-10-04 | 2015-06-01 | Univ Nat Taiwan Science Tech | Real-time physiological signal measurement and feedback system |
US9943269B2 (en) | 2011-10-13 | 2018-04-17 | Masimo Corporation | System for displaying medical monitoring data |
US9808188B1 (en) | 2011-10-13 | 2017-11-07 | Masimo Corporation | Robust fractional saturation determination |
EP3603502B1 (en) | 2011-10-13 | 2023-10-04 | Masimo Corporation | Physiological acoustic monitoring system |
WO2013056160A2 (en) | 2011-10-13 | 2013-04-18 | Masimo Corporation | Medical monitoring hub |
US9778079B1 (en) | 2011-10-27 | 2017-10-03 | Masimo Corporation | Physiological monitor gauge panel |
TWI476641B (en) | 2011-11-22 | 2015-03-11 | Pixart Imaging Inc | Remote controller and display system |
US9445759B1 (en) | 2011-12-22 | 2016-09-20 | Cercacor Laboratories, Inc. | Blood glucose calibration system |
US9392945B2 (en) | 2012-01-04 | 2016-07-19 | Masimo Corporation | Automated CCHD screening and detection |
WO2013106607A2 (en) | 2012-01-10 | 2013-07-18 | Maxim Integrated Products, Inc. | Heart rate and blood oxygen monitoring system |
US9848787B2 (en) * | 2012-02-07 | 2017-12-26 | Laser Associated Sciences, Inc. | Perfusion assessment using transmission laser speckle imaging |
US9267572B2 (en) | 2012-02-08 | 2016-02-23 | Masimo Corporation | Cable tether system |
US9480435B2 (en) | 2012-02-09 | 2016-11-01 | Masimo Corporation | Configurable patient monitoring system |
US10307111B2 (en) | 2012-02-09 | 2019-06-04 | Masimo Corporation | Patient position detection system |
US10149616B2 (en) | 2012-02-09 | 2018-12-11 | Masimo Corporation | Wireless patient monitoring device |
US9195385B2 (en) | 2012-03-25 | 2015-11-24 | Masimo Corporation | Physiological monitor touchscreen interface |
JP6490577B2 (en) | 2012-04-17 | 2019-03-27 | マシモ・コーポレイション | How to operate a pulse oximeter device |
US20130296672A1 (en) | 2012-05-02 | 2013-11-07 | Masimo Corporation | Noninvasive physiological sensor cover |
US9220409B2 (en) | 2012-05-31 | 2015-12-29 | Covidien Lp | Optical instrument with ambient light removal |
WO2013184965A1 (en) | 2012-06-07 | 2013-12-12 | Masimo Corporation | Depth of consciousness monitor |
US8948832B2 (en) | 2012-06-22 | 2015-02-03 | Fitbit, Inc. | Wearable heart rate monitor |
US8954135B2 (en) | 2012-06-22 | 2015-02-10 | Fitbit, Inc. | Portable biometric monitoring devices and methods of operating same |
WO2014018447A1 (en) | 2012-07-24 | 2014-01-30 | Stryker Corporation | Surgical instrument that, in real time, is adjustably bendable |
US9697928B2 (en) | 2012-08-01 | 2017-07-04 | Masimo Corporation | Automated assembly sensor cable |
CN103630506B (en) | 2012-08-20 | 2016-10-26 | 台医光电科技股份有限公司 | Detection module and detection device |
US9392976B2 (en) | 2012-09-11 | 2016-07-19 | Covidien Lp | Methods and systems for determining physiological information based on a combined autocorrelation sequence |
US9877650B2 (en) | 2012-09-20 | 2018-01-30 | Masimo Corporation | Physiological monitor with mobile computing device connectivity |
USD692145S1 (en) | 2012-09-20 | 2013-10-22 | Masimo Corporation | Medical proximity detection token |
US9749232B2 (en) | 2012-09-20 | 2017-08-29 | Masimo Corporation | Intelligent medical network edge router |
US9955937B2 (en) | 2012-09-20 | 2018-05-01 | Masimo Corporation | Acoustic patient sensor coupler |
US20140180160A1 (en) | 2012-10-12 | 2014-06-26 | Emery N. Brown | System and method for monitoring and controlling a state of a patient during and after administration of anesthetic compound |
US9717458B2 (en) | 2012-10-20 | 2017-08-01 | Masimo Corporation | Magnetic-flap optical sensor |
US9560996B2 (en) | 2012-10-30 | 2017-02-07 | Masimo Corporation | Universal medical system |
US9787568B2 (en) | 2012-11-05 | 2017-10-10 | Cercacor Laboratories, Inc. | Physiological test credit method |
US10447844B2 (en) | 2012-12-14 | 2019-10-15 | Apple Inc. | Method and apparatus for automatically setting alarms and notifications |
US9311382B2 (en) | 2012-12-14 | 2016-04-12 | Apple Inc. | Method and apparatus for personal characterization data collection using sensors |
US20140166076A1 (en) | 2012-12-17 | 2014-06-19 | Masimo Semiconductor, Inc | Pool solar power generator |
US9750461B1 (en) | 2013-01-02 | 2017-09-05 | Masimo Corporation | Acoustic respiratory monitoring sensor with probe-off detection |
US20140221854A1 (en) | 2013-01-08 | 2014-08-07 | National Electronics and Watch Company | Measuring device, including a heart rate sensor, configured to be worn on the wrist of a user |
US9724025B1 (en) | 2013-01-16 | 2017-08-08 | Masimo Corporation | Active-pulse blood analysis system |
US9210566B2 (en) | 2013-01-18 | 2015-12-08 | Apple Inc. | Method and apparatus for automatically adjusting the operation of notifications based on changes in physical activity level |
ITMI20130104A1 (en) | 2013-01-24 | 2014-07-25 | Empatica Srl | DEVICE, SYSTEM AND METHOD FOR THE DETECTION AND TREATMENT OF HEART SIGNALS |
US9750442B2 (en) | 2013-03-09 | 2017-09-05 | Masimo Corporation | Physiological status monitor |
KR101788428B1 (en) | 2013-03-11 | 2017-10-19 | 애플 인크. | Portable electronic device using a tactile vibrator |
US20140276014A1 (en) | 2013-03-13 | 2014-09-18 | Cephalogics, LLC | Supports for optical sensors and related apparatus and methods |
WO2014164139A1 (en) | 2013-03-13 | 2014-10-09 | Masimo Corporation | Systems and methods for monitoring a patient health network |
US20150005600A1 (en) | 2013-03-13 | 2015-01-01 | Cercacor Laboratories, Inc. | Finger-placement sensor tape |
WO2014159132A1 (en) | 2013-03-14 | 2014-10-02 | Cercacor Laboratories, Inc. | Systems and methods for testing patient monitors |
EP4032469A1 (en) | 2013-03-14 | 2022-07-27 | Spry Health, Inc. | Systems and methods of multispectral blood measurement |
US9936917B2 (en) | 2013-03-14 | 2018-04-10 | Masimo Laboratories, Inc. | Patient monitor placement indicator |
WO2014158820A1 (en) | 2013-03-14 | 2014-10-02 | Cercacor Laboratories, Inc. | Patient monitor as a minimally invasive glucometer |
US20140275871A1 (en) | 2013-03-14 | 2014-09-18 | Cercacor Laboratories, Inc. | Wireless optical communication between noninvasive physiological sensors and patient monitors |
US9986952B2 (en) | 2013-03-14 | 2018-06-05 | Masimo Corporation | Heart sound simulator |
US10456038B2 (en) | 2013-03-15 | 2019-10-29 | Cercacor Laboratories, Inc. | Cloud-based physiological monitoring system |
CN104055504A (en) | 2013-03-18 | 2014-09-24 | 精工爱普生株式会社 | Biological Information Detection Apparatus |
WO2014176356A1 (en) | 2013-04-23 | 2014-10-30 | The General Hospital Corporation | System and method for monitoring anesthesia and sedation using measures of brain coherence and synchrony |
WO2014176349A1 (en) | 2013-04-23 | 2014-10-30 | The General Hospital Corporation | Monitoring brain metabolism and activity using electroencephalogram and optical imaging |
US20140323898A1 (en) | 2013-04-24 | 2014-10-30 | Patrick L. Purdon | System and Method for Monitoring Level of Dexmedatomidine-Induced Sedation |
WO2014176436A1 (en) | 2013-04-24 | 2014-10-30 | The General Hospital Corporation | System and method for estimating high time-frequency resolution eeg spectrograms to monitor patient state |
WO2014178793A1 (en) | 2013-04-29 | 2014-11-06 | Heptagon Micro Optics Pte. Ltd. | Wristwatch including an integrated pulse oximeter or other modules that sense physiological data |
FI126338B (en) | 2013-05-15 | 2016-10-14 | Pulseon Oy | Portable heart rate monitor |
WO2014210527A1 (en) | 2013-06-28 | 2014-12-31 | The General Hospital Corporation | System and method to infer brain state during burst suppression |
WO2015001434A1 (en) | 2013-07-01 | 2015-01-08 | Seraphim Sense Ltd. | Wearable health sensor |
US9339236B2 (en) | 2013-07-05 | 2016-05-17 | James Tyler Frix | Continuous transdermal monitoring system and method |
US9891079B2 (en) | 2013-07-17 | 2018-02-13 | Masimo Corporation | Pulser with double-bearing position encoder for non-invasive physiological monitoring |
WO2015020911A2 (en) | 2013-08-05 | 2015-02-12 | Cercacor Laboratories, Inc. | Blood pressure monitor with valve-chamber assembly |
US20150065889A1 (en) | 2013-09-02 | 2015-03-05 | Life Beam Technologies Ltd. | Bodily worn multiple optical sensors heart rate measuring device and method |
WO2015038683A2 (en) | 2013-09-12 | 2015-03-19 | Cercacor Laboratories, Inc. | Medical device management system |
EP3043696B1 (en) | 2013-09-13 | 2022-11-02 | The General Hospital Corporation | Systems and methods for improved brain monitoring during general anesthesia and sedation |
US10010276B2 (en) | 2013-10-07 | 2018-07-03 | Masimo Corporation | Regional oximetry user interface |
US10832818B2 (en) | 2013-10-11 | 2020-11-10 | Masimo Corporation | Alarm notification system |
US20160256082A1 (en) | 2013-10-21 | 2016-09-08 | Apple Inc. | Sensors and applications |
US9504405B2 (en) | 2013-10-23 | 2016-11-29 | Verily Life Sciences Llc | Spatial modulation of magnetic particles in vasculature by external magnetic field |
US10478075B2 (en) | 2013-10-25 | 2019-11-19 | Qualcomm Incorporated | System and method for obtaining bodily function measurements using a mobile device |
US20160019360A1 (en) | 2013-12-04 | 2016-01-21 | Apple Inc. | Wellness aggregator |
WO2015084375A1 (en) | 2013-12-05 | 2015-06-11 | Apple Inc. | Method of reducing motion artifacts on wearable optical sensor devices |
US20160287181A1 (en) | 2013-12-05 | 2016-10-06 | Apple Inc. | Wearable multi-modal physiological sensing system |
KR20150067047A (en) | 2013-12-09 | 2015-06-17 | 삼성전자주식회사 | Modular sensor platform |
US10279247B2 (en) | 2013-12-13 | 2019-05-07 | Masimo Corporation | Avatar-incentive healthcare therapy |
US11298075B2 (en) | 2013-12-19 | 2022-04-12 | Apple Inc. | Physiological monitoring method and system |
US9593969B2 (en) | 2013-12-27 | 2017-03-14 | Apple Inc. | Concealed electrical connectors |
US20160296173A1 (en) | 2013-12-30 | 2016-10-13 | Apple Inc. | Motion artifact cancelation |
WO2015102588A1 (en) | 2013-12-30 | 2015-07-09 | Apple Inc. | User identification system based on plethysmography |
US20170164884A1 (en) | 2013-12-30 | 2017-06-15 | Apple Inc. | Measuring respiration rate with multi-band plethysmography |
EP3013217B1 (en) | 2014-01-07 | 2017-02-22 | Opsolution GmbH | Device and method for determining a concentration in a sample |
US11259745B2 (en) | 2014-01-28 | 2022-03-01 | Masimo Corporation | Autonomous drug delivery system |
US10086138B1 (en) | 2014-01-28 | 2018-10-02 | Masimo Corporation | Autonomous drug delivery system |
US20160287107A1 (en) | 2014-01-30 | 2016-10-06 | Intel Corporation | Intelligent photoplethysmograph signal-to-noise ratio control for recovery of biosignals during times of motion |
KR20160108491A (en) | 2014-01-31 | 2016-09-19 | 애플 인크. | Wearing dependent operation of wearable device |
JP6085725B2 (en) | 2014-02-04 | 2017-02-22 | コーニンクレッカ フィリップス エヌ ヴェKoninklijke Philips N.V. | Optical device that measures the user's heart rate |
US10285626B1 (en) | 2014-02-14 | 2019-05-14 | Apple Inc. | Activity identification using an optical heart rate monitor |
US10532174B2 (en) | 2014-02-21 | 2020-01-14 | Masimo Corporation | Assistive capnography device |
EP3113670B1 (en) | 2014-03-06 | 2020-05-27 | Koninklijke Philips N.V. | Physiological property determination apparatus and method |
US10058254B2 (en) | 2014-04-07 | 2018-08-28 | Physical Enterprises Inc. | Systems and methods for optical sensor arrangements |
US10060788B2 (en) * | 2014-04-07 | 2018-08-28 | Physical Enterprises Inc. | Systems and methods for monitoring physiological parameters |
WO2015159692A1 (en) | 2014-04-14 | 2015-10-22 | 株式会社村田製作所 | Pulse wave propagation time measurement device and biological state estimation device |
US10164688B2 (en) | 2014-04-30 | 2018-12-25 | Apple Inc. | Actuator assisted alignment of connectible devices |
RU2016151983A (en) | 2014-05-28 | 2018-07-02 | Конинклейке Филипс Н.В. | Reducing motion artifacts using multi-channel PPG signals |
US9867575B2 (en) | 2014-08-22 | 2018-01-16 | Apple Inc. | Heart rate path optimizer |
US9848823B2 (en) | 2014-05-29 | 2017-12-26 | Apple Inc. | Context-aware heart rate estimation |
US11107578B2 (en) | 2014-05-30 | 2021-08-31 | Apple Inc. | Systems and methods for facilitating health research |
WO2015187732A1 (en) | 2014-06-03 | 2015-12-10 | The Texas A&M University System | Optical sensor for health monitoring |
US9924897B1 (en) | 2014-06-12 | 2018-03-27 | Masimo Corporation | Heated reprocessing of physiological sensors |
US10231670B2 (en) | 2014-06-19 | 2019-03-19 | Masimo Corporation | Proximity sensor in pulse oximeter |
US10039491B2 (en) | 2014-06-30 | 2018-08-07 | Verily Life Sciences Llc | Methods for reducing noise in optical biological sensors |
US20170172476A1 (en) | 2014-06-30 | 2017-06-22 | Scint B.V. | Body worn measurement device |
TWI530276B (en) | 2014-07-08 | 2016-04-21 | 原相科技股份有限公司 | Biometric detection module with denoising function and biometric detection method thereof |
EP3171756A1 (en) | 2014-07-22 | 2017-05-31 | Koninklijke Philips N.V. | Unobtrusive skin tissue hydration determining device and related method |
WO2016014833A1 (en) | 2014-07-23 | 2016-01-28 | Goodix Technology Inc. | Optical heart rate sensor |
US10265024B2 (en) | 2014-07-26 | 2019-04-23 | Salutron, Inc. | Sensor system for heart rate measurement per axis of shared orientation |
US10165954B2 (en) | 2014-07-31 | 2019-01-01 | Salutron Inc. | Integrated sensor modules |
US20160041531A1 (en) | 2014-08-06 | 2016-02-11 | Quanttus, Inc. | Biofeedback watches |
EP4098178B1 (en) | 2014-08-06 | 2024-04-10 | Yukka Magic LLC | Optical physiological sensor modules with reduced signal noise |
JP6296938B2 (en) | 2014-08-07 | 2018-03-20 | インターナショナル・ビジネス・マシーンズ・コーポレーションInternational Business Machines Corporation | Authentication using a two-dimensional code on a mobile device |
US10758133B2 (en) | 2014-08-07 | 2020-09-01 | Apple Inc. | Motion artifact removal by time domain projection |
US10201286B2 (en) | 2014-08-22 | 2019-02-12 | Apple Inc. | Frequency domain projection algorithm |
US20160051158A1 (en) | 2014-08-22 | 2016-02-25 | Apple Inc. | Harmonic template classifier |
JP5862731B1 (en) | 2014-08-27 | 2016-02-16 | セイコーエプソン株式会社 | Sensor and biological information detection apparatus |
US10092197B2 (en) | 2014-08-27 | 2018-10-09 | Apple Inc. | Reflective surfaces for PPG signal detection |
US10066970B2 (en) | 2014-08-27 | 2018-09-04 | Apple Inc. | Dynamic range control for optical encoders |
US10078052B2 (en) | 2014-08-28 | 2018-09-18 | Apple Inc. | Reflective surface treatments for optical sensors |
DE202015006142U1 (en) | 2014-09-02 | 2015-12-09 | Apple Inc. | Electronic touch communication |
US10154789B2 (en) | 2014-09-02 | 2018-12-18 | Apple Inc. | Latent load calibration for calorimetry using sensor fusion |
CN205121417U (en) | 2014-09-02 | 2016-03-30 | 苹果公司 | Wearable electronic device |
US10215698B2 (en) | 2014-09-02 | 2019-02-26 | Apple Inc. | Multiple light paths architecture and obscuration methods for signal and perfusion index optimization |
US10231657B2 (en) | 2014-09-04 | 2019-03-19 | Masimo Corporation | Total hemoglobin screening sensor |
WO2016040263A1 (en) | 2014-09-08 | 2016-03-17 | Braintree Analytics Llc | Wrist worn accelerometer for pulse transit time (ptt) measurements of blood pressure |
US10702171B2 (en) | 2014-09-08 | 2020-07-07 | Apple Inc. | Systems, devices, and methods for measuring blood pressure of a user |
WO2016040264A1 (en) | 2014-09-08 | 2016-03-17 | Braintree Analytics Llc | Electrical coupling of pulse transit time (ptt) measurement system to heart for blood pressure measurment |
CN107106054B (en) | 2014-09-08 | 2021-11-02 | 苹果公司 | Blood pressure monitoring using multifunctional wrist-worn device |
US10219754B1 (en) | 2014-09-09 | 2019-03-05 | Apple Inc. | Modulation and demodulation techniques for a health monitoring system |
US10593186B2 (en) | 2014-09-09 | 2020-03-17 | Apple Inc. | Care event detection and alerts |
US10383520B2 (en) | 2014-09-18 | 2019-08-20 | Masimo Semiconductor, Inc. | Enhanced visible near-infrared photodiode and non-invasive physiological sensor |
US9723997B1 (en) | 2014-09-26 | 2017-08-08 | Apple Inc. | Electronic device that computes health data |
US9553625B2 (en) | 2014-09-27 | 2017-01-24 | Apple Inc. | Modular functional band links for wearable devices |
US9952095B1 (en) | 2014-09-29 | 2018-04-24 | Apple Inc. | Methods and systems for modulation and demodulation of optical signals |
WO2016057553A1 (en) | 2014-10-07 | 2016-04-14 | Masimo Corporation | Modular physiological sensors |
KR102269797B1 (en) | 2014-10-08 | 2021-06-28 | 엘지전자 주식회사 | Wearable device |
EP3015062A1 (en) | 2014-10-30 | 2016-05-04 | ams AG | Optical sensor arrangement for an optical measurement of biological parameters and watch comprising the optical sensor arrangement |
CN107249443A (en) | 2014-12-05 | 2017-10-13 | 苹果公司 | Sleep measurement computer system |
KR102575058B1 (en) | 2015-01-23 | 2023-09-05 | 마시모 스웨덴 에이비 | Nasal/Oral Cannula Systems and Manufacturing |
JP6766052B2 (en) | 2015-01-27 | 2020-10-07 | アップル インコーポレイテッドApple Inc. | Systems and methods for determining sleep quality |
MX2017010045A (en) | 2015-02-06 | 2018-04-10 | Masimo Corp | Connector assembly with pogo pins for use with medical sensors. |
US10568553B2 (en) | 2015-02-06 | 2020-02-25 | Masimo Corporation | Soft boot pulse oximetry sensor |
KR102609605B1 (en) | 2015-02-06 | 2023-12-05 | 마시모 코오퍼레이션 | Fold flex circuit for optical probes |
USD755392S1 (en) | 2015-02-06 | 2016-05-03 | Masimo Corporation | Pulse oximetry sensor |
US9696199B2 (en) | 2015-02-13 | 2017-07-04 | Taiwan Biophotonic Corporation | Optical sensor |
US10244948B2 (en) | 2015-03-06 | 2019-04-02 | Apple Inc. | Statistical heart rate monitoring for estimating calorie expenditure |
US9651405B1 (en) | 2015-03-06 | 2017-05-16 | Apple Inc. | Dynamic adjustment of a sampling rate for an optical encoder |
US10055121B2 (en) | 2015-03-07 | 2018-08-21 | Apple Inc. | Activity based thresholds and feedbacks |
US9781984B2 (en) | 2015-03-08 | 2017-10-10 | Apple Inc. | Dynamic fit adjustment for wearable electronic devices |
WO2016176218A1 (en) | 2015-04-27 | 2016-11-03 | Apple Inc. | Dynamically reconfigurable apertures for optimization of ppg signal and ambient light mitigation |
US10524738B2 (en) | 2015-05-04 | 2020-01-07 | Cercacor Laboratories, Inc. | Noninvasive sensor system with visual infographic display |
WO2016191307A1 (en) | 2015-05-22 | 2016-12-01 | Cercacor Laboratories, Inc. | Non-invasive optical physiological differential pathlength sensor |
WO2016205549A1 (en) | 2015-06-16 | 2016-12-22 | Braintree Analytics Llc | Cuff designs and methods |
US10448871B2 (en) | 2015-07-02 | 2019-10-22 | Masimo Corporation | Advanced pulse oximetry sensor |
US20170024748A1 (en) | 2015-07-22 | 2017-01-26 | Patient Doctor Technologies, Inc. | Guided discussion platform for multiple parties |
EP3334334A1 (en) | 2015-08-11 | 2018-06-20 | Masimo Corporation | Medical monitoring analysis and replay including indicia responsive to light attenuated by body tissue |
AU2016315947B2 (en) | 2015-08-31 | 2021-02-18 | Masimo Corporation | Wireless patient monitoring systems and methods |
US10699594B2 (en) | 2015-09-16 | 2020-06-30 | Apple Inc. | Calculating an estimate of wind resistance experienced by a cyclist |
US9716937B2 (en) | 2015-09-16 | 2017-07-25 | Apple Inc. | Earbuds with biometric sensing |
US10108151B2 (en) | 2015-09-21 | 2018-10-23 | Apple Inc. | Indicators for wearable electronic devices |
US9939899B2 (en) | 2015-09-25 | 2018-04-10 | Apple Inc. | Motion and gesture input from a wearable device |
US10206623B2 (en) | 2015-09-28 | 2019-02-19 | Apple Inc. | Band tightness sensor of a wearable device |
US10285645B2 (en) | 2015-09-28 | 2019-05-14 | Apple Inc. | Sensing contact force related to user wearing an electronic device |
US20170094450A1 (en) | 2015-09-30 | 2017-03-30 | Apple Inc. | Crowdsourcing activity detection for group activities |
US20170086689A1 (en) | 2015-09-30 | 2017-03-30 | Apple Inc. | Electronic device including ambient light compensation circuit for heart rate generation and related methods |
US11679579B2 (en) | 2015-12-17 | 2023-06-20 | Masimo Corporation | Varnish-coated release liner |
US20170251974A1 (en) | 2016-03-04 | 2017-09-07 | Masimo Corporation | Nose sensor |
US10537285B2 (en) | 2016-03-04 | 2020-01-21 | Masimo Corporation | Nose sensor |
US10039080B2 (en) | 2016-03-04 | 2018-07-31 | Apple Inc. | Situationally-aware alerts |
US10993662B2 (en) | 2016-03-04 | 2021-05-04 | Masimo Corporation | Nose sensor |
US10694994B2 (en) | 2016-03-22 | 2020-06-30 | Apple Inc. | Techniques for jointly calibrating load and aerobic capacity |
US20170293727A1 (en) | 2016-04-08 | 2017-10-12 | Apple Inc. | Intelligent blood pressure monitoring |
US11191484B2 (en) | 2016-04-29 | 2021-12-07 | Masimo Corporation | Optical sensor tape |
US20170325744A1 (en) | 2016-05-10 | 2017-11-16 | Apple Inc. | Systems and methods for increasing localized pressure to improve ppg motion performance |
KR102203563B1 (en) | 2016-05-10 | 2021-01-15 | 애플 인크. | Systems and methods for measuring non-pulsatile blood volume |
US10687707B2 (en) | 2016-06-07 | 2020-06-23 | Apple Inc. | Detecting activity by a wheelchair user |
US11033708B2 (en) | 2016-06-10 | 2021-06-15 | Apple Inc. | Breathing sequence user interface |
US11069255B2 (en) | 2016-06-10 | 2021-07-20 | Apple Inc. | Fluctuating progress indicator |
US10504380B2 (en) | 2016-06-10 | 2019-12-10 | Apple Inc. | Managing presentation of fitness achievements |
US10726731B2 (en) | 2016-06-10 | 2020-07-28 | Apple Inc. | Breathing synchronization and monitoring |
US9866671B1 (en) | 2016-06-21 | 2018-01-09 | Apple Inc. | Tracking activity data between wearable devices paired with a companion device |
US10608817B2 (en) | 2016-07-06 | 2020-03-31 | Masimo Corporation | Secure and zero knowledge data sharing for cloud applications |
US10617302B2 (en) | 2016-07-07 | 2020-04-14 | Masimo Corporation | Wearable pulse oximeter and respiration monitor |
US10702211B2 (en) | 2016-07-15 | 2020-07-07 | Apple Inc. | Sensor window with integrated isolation feature |
US11210583B2 (en) | 2016-07-20 | 2021-12-28 | Apple Inc. | Using proxies to enable on-device machine learning |
US10512432B2 (en) | 2016-08-12 | 2019-12-24 | Apple Inc. | Vital signs monitoring system |
US20180049694A1 (en) | 2016-08-16 | 2018-02-22 | Apple Inc. | Systems and methods for determining individualized energy expenditure |
US10709933B2 (en) | 2016-08-17 | 2020-07-14 | Apple Inc. | Pose and heart rate energy expenditure for yoga |
US10687752B2 (en) | 2016-08-29 | 2020-06-23 | Apple Inc. | Detecting unmeasurable loads using heart rate and work rate |
US10617912B2 (en) | 2016-08-31 | 2020-04-14 | Apple Inc. | Systems and methods of swimming calorimetry |
US10512406B2 (en) | 2016-09-01 | 2019-12-24 | Apple Inc. | Systems and methods for determining an intensity level of an exercise using photoplethysmogram (PPG) |
WO2018057937A1 (en) | 2016-09-22 | 2018-03-29 | Apple Inc. | Systems and methods for determining physiological signals using ambient light |
US10736543B2 (en) | 2016-09-22 | 2020-08-11 | Apple Inc. | Workout monitor interface |
WO2018071715A1 (en) | 2016-10-13 | 2018-04-19 | Masimo Corporation | Systems and methods for patient fall detection |
US10750984B2 (en) | 2016-12-22 | 2020-08-25 | Cercacor Laboratories, Inc. | Methods and devices for detecting intensity of light with translucent detector |
US10721785B2 (en) | 2017-01-18 | 2020-07-21 | Masimo Corporation | Patient-worn wireless physiological sensor with pairing functionality |
US10918322B2 (en) | 2017-02-13 | 2021-02-16 | Apple Inc. | Light restriction designs in optical sensing applications having shared windows |
US10327713B2 (en) | 2017-02-24 | 2019-06-25 | Masimo Corporation | Modular multi-parameter patient monitoring device |
US11086609B2 (en) | 2017-02-24 | 2021-08-10 | Masimo Corporation | Medical monitoring hub |
WO2018156648A1 (en) | 2017-02-24 | 2018-08-30 | Masimo Corporation | Managing dynamic licenses for physiological parameters in a patient monitoring environment |
WO2018156809A1 (en) | 2017-02-24 | 2018-08-30 | Masimo Corporation | Augmented reality system for displaying patient data |
WO2018156804A1 (en) | 2017-02-24 | 2018-08-30 | Masimo Corporation | System for displaying medical monitoring data |
US10388120B2 (en) | 2017-02-24 | 2019-08-20 | Masimo Corporation | Localized projection of audible noises in medical settings |
CN110891486A (en) | 2017-03-10 | 2020-03-17 | 梅西莫股份有限公司 | Pneumonia screening instrument |
US10524735B2 (en) | 2017-03-28 | 2020-01-07 | Apple Inc. | Detecting conditions using heart rate sensors |
WO2018194992A1 (en) | 2017-04-18 | 2018-10-25 | Masimo Corporation | Nose sensor |
USD822215S1 (en) | 2017-04-26 | 2018-07-03 | Masimo Corporation | Medical monitoring device |
US10918281B2 (en) | 2017-04-26 | 2021-02-16 | Masimo Corporation | Medical monitoring device having multiple configurations |
EP3614909B1 (en) | 2017-04-28 | 2024-04-03 | Masimo Corporation | Spot check measurement system |
USD835284S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
USD835283S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
USD835285S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
USD835282S1 (en) | 2017-04-28 | 2018-12-04 | Masimo Corporation | Medical monitoring device |
USD822216S1 (en) | 2017-04-28 | 2018-07-03 | Masimo Corporation | Medical monitoring device |
WO2018208616A1 (en) | 2017-05-08 | 2018-11-15 | Masimo Corporation | System for pairing a medical system to a network controller by use of a dongle |
USD833624S1 (en) | 2017-05-09 | 2018-11-13 | Masimo Corporation | Medical device |
US11026604B2 (en) | 2017-07-13 | 2021-06-08 | Cercacor Laboratories, Inc. | Medical monitoring device for harmonizing physiological measurements |
US10637181B2 (en) | 2017-08-15 | 2020-04-28 | Masimo Corporation | Water resistant connector for noninvasive patient monitor |
EP4039177A1 (en) | 2017-10-19 | 2022-08-10 | Masimo Corporation | Display arrangement for medical monitoring system |
-
2016
- 2016-06-28 US US15/195,199 patent/US10448871B2/en active Active
- 2016-06-29 JP JP2017565276A patent/JP7004575B2/en active Active
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US10470695B2 (en) | 2019-11-12 |
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